Sensing Module Having A Piezo-Resistive Sensor For Orthopedic Load Sensing Insert Device

ABSTRACT

A sensing insert device ( 100 ) is disclosed for measuring a parameter of the muscular-skeletal system. The sensing insert device ( 100 ) can be temporary or permanent. Used intra-operatively, the sensing insert device ( 100 ) comprises an insert dock ( 202 ) and a sensing module ( 200 ). The sensing module ( 200 ) is a self-contained encapsulated measurement device having at least one contacting surface that couples to the muscular-skeletal system. The sensing module ( 200 ) comprises one or more sensing assemblages, electronic circuitry ( 307 ), an antenna ( 2302 ), and communication circuitry ( 320 ). The sensing assemblages are between a top plate ( 1502 ) and a bottom plate ( 1504 ) in a sensing platform ( 121 ). The sensing assemblages comprise a load disc ( 2004 ) and a piezo-resistive sensor ( 2002 ) to measure the parameter. An elastic support structure or springs ( 1108 ) is coupled between the top plate ( 1502 ) and the bottom plate ( 1504 ) to prevent cantilevering of a surface.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of application Ser. No. 12/826,349filed on Jun. 29, 2010 the content of which is hereby incorporated byreference in its entirety.

FIELD

The present invention pertains generally to a joint prosthesis, andparticularly to methods and devices for assessing and determining properalignment and placement of an implant component or components duringjoint reconstructive surgery and long-term implantation.

BACKGROUND

The skeletal system of a mammal is subject to variations among species.Further changes can occur due to environmental factors, degradationthrough use, and aging. An orthopedic joint of the skeletal systemtypically comprises two or more bones that move in relation to oneanother. Movement is enabled by muscle tissue and tendons attached tothe skeletal system of the joint. Ligaments hold and stabilize the oneor more joint bones positionally. Cartilage is a wear surface thatprevents bone-to-bone contact, distributes load, and lowers friction.

There has been substantial growth in the repair of the human skeletalsystem. In general, orthopedic joints have evolved using informationfrom simulations, mechanical prototypes, and patient data that iscollected and used to initiate improved designs. Similarly, the toolsbeing used for orthopedic surgery have been refined over the years buthave not changed substantially. Thus, the basic procedure forreplacement of an orthopedic joint has been standardized to meet thegeneral needs of a wide distribution of the population. Although thetools, procedure, and artificial joint meet a general need, eachreplacement procedure is subject to significant variation from patientto patient. The correction of these individual variations relies on theskill of the surgeon to adapt and fit the replacement joint using theavailable tools to the specific circumstance.

BRIEF DESCRIPTION OF THE DRAWINGS

Various features of the system are set forth with particularity in theappended claims. The embodiments herein, can be understood by referenceto the following description, taken in conjunction with the accompanyingdrawings, in which:

FIG. 1 is an illustration of an application of sensing insert device inaccordance with an exemplary embodiment;

FIG. 2 is an illustration of a sensing insert device placed in a jointof the muscular-skeletal system for measuring a parameter in accordancewith an exemplary embodiment;

FIG. 3 is a perspective view of a medical sensing platform comprising anencapsulating enclosure in accordance with one embodiment;

FIG. 4 is a perspective view of a medical sensing device suitable foruse as a bi-compartmental implant and comprising an encapsulatingenclosure in accordance with one embodiment;

FIG. 5 is an exemplary block diagram of the components of the sensingmodule in accordance with an exemplary embodiment;

FIG. 6 is a diagram of an exemplary communications system forshort-range telemetry according to one embodiment;

FIG. 7 is an illustration of a block model diagram of the sensing modulein accordance with an exemplary embodiment;

FIG. 8 is an exemplary assemblage that illustrates propagation ofultrasound waves within the waveguide in the bi-directional mode ofoperation of this assemblage in accordance with one embodiment;

FIG. 9 is an exemplary cross-sectional view of an ultrasound waveguideto illustrate changes in the propagation of ultrasound waves withchanges in the length of the waveguide in accordance with oneembodiment;

FIG. 10 is an exemplary block diagram of a propagation tuned oscillator(PTO) to maintain positive closed-loop feedback in accordance with anexemplary embodiment;

FIG. 11 is a cross-sectional view of a layout architecture of thesensing module in accordance with an exemplary embodiment;

FIG. 12 is a simplified cross-sectional view of an embodiment of theload sensing platform in accordance with an exemplary embodiment;

FIG. 13 is an illustration of an exemplary data packet containing sensordata;

FIG. 14 is an exemplary block diagram schematic of a compact low-powerenergy source integrated into an exemplary electronic assembly of thesensing module in accordance with one embodiment;

FIG. 15 is a partial cross-section schematic side view of a sensingplatform including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment;

FIG. 16 is a partial cross-section schematic side view of the sensingplatform including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment;

FIG. 17 is a partial cross-section schematic side view of a sensingmodule including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment;

FIG. 18 is a cross-sectional view of the sensing module having a smallform factor in accordance with an exemplary embodiment;

FIG. 19 is a perspective view of the interconnect stack of the sensingmodule in accordance with an exemplary embodiment;

FIG. 20 is a partial cross-section schematic side view of a sensingplatform including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment;

FIG. 21 is a partial cross-section schematic side view of the sensingplatform including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment;

FIG. 22 is a partial cross-section schematic side view of a sensingmodule including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment;

FIG. 23 is a perspective view of an exemplary loop antenna in accordancewith one embodiment;

FIG. 24 is a perspective view of an integrated loop antenna according toanother embodiment;

FIG. 25 Illustrates by way of example a plot of normalized radiatedfield strength versus frequency performance of an example loop antennaintegrated into a flexible substrate of the electronic circuit board;

FIG. 26 Illustrates a radiation pattern of the loop antenna integratedinto a flexible substrate of an electronic circuit in accordance with anexemplary embodiment;

FIG. 27 illustrates a low power consumption integrated transducer drivercircuit in accordance with an exemplary embodiment;

FIG. 28 illustrates a block diagram of an edge-detect receiver circuitin accordance with an exemplary embodiment;

FIG. 29 is a block diagram of a zero-crossing receiver in accordancewith one embodiment;

FIG. 30 is a sensor interface diagram incorporating the zero-crossingreceiver in a continuous wave multiplexing arrangement for maintainingpositive closed-loop feedback in accordance with one embodiment;

FIG. 31 is an exemplary block diagram of a propagation tuned oscillator(PTO) incorporating the zero-crossing receiver for operation incontinuous wave mode;

FIG. 32 is a sensor interface diagram incorporating the integratedzero-crossing receiver in a pulse multiplexing arrangement formaintaining positive closed-loop feedback in accordance with oneembodiment;

FIG. 33 is an exemplary block diagram of a propagation tuned oscillator(PTO) incorporating the zero-crossing receiver for operation in pulsemode in accordance with one embodiment;

FIG. 34 is a sensor interface diagram incorporating the edge-detectreceiver circuit in a pulse-echo multiplexing arrangement formaintaining positive closed-loop feedback in accordance with oneembodiment;

FIG. 35 is an exemplary block diagram of a propagation tuned oscillator(PTO) incorporating the edge-detect receiver circuit for operation inpulse echo mode in accordance with one embodiment;

FIG. 36 is a final insert in accordance with an exemplary embodiment;

FIG. 37 is a perspective view of sensing modules in final insert inaccordance with an exemplary embodiment; and

FIG. 38 is an illustration of the final insert installed in a knee inaccordance with an exemplary embodiment.

DETAILED DESCRIPTION

Embodiments of the invention are broadly directed to measurement ofphysical parameters. Many physical parameters of interest withinphysical systems or bodies can be measured by evaluating changes in thecharacteristics of energy waves or pulses. As one example, changes inthe transit time or shape of an energy wave or pulse propagating througha changing medium can be measured to determine the forces acting on themedium and causing the changes. The propagation velocity of the energywaves or pulses in the medium is affected by physical changes in of themedium. The physical parameter or parameters of interest can include,but are not limited to, measurement of load, force, pressure,displacement, density, viscosity, localized temperature. Theseparameters can be evaluated by measuring changes in the propagation timeof energy pulses or waves relative to orientation, alignment, direction,or position as well as movement, rotation, or acceleration along an axisor combination of axes by wireless sensing modules or devices positionedon or within a body, instrument, appliance, vehicle, equipment, or otherphysical system.

In all of the examples illustrated and discussed herein, any specificmaterials, temperatures, times, energies etc. . . . for process steps orspecific structure implementations should be interpreted to beillustrative only and non-limiting. Processes, techniques, apparatus,and materials as known by one of ordinary skill in the art may not bediscussed in detail but are intended to be part of an enablingdescription where appropriate.

Note that similar reference numerals and letters refer to similar itemsin the following figures. In some cases, numbers from priorillustrations will not be placed on subsequent figures for purposes ofclarity. In general, it should be assumed that structures not identifiedin a figure are the same as previous prior figures.

In the present invention these parameters are measured with anintegrated wireless sensing module or device comprising an i)encapsulating structure that supports sensors and contacting surfacesand ii) an electronic assemblage that integrates a power supply, sensingelements, ultrasound resonator or resonators or transducer ortransducers and ultrasound waveguide or waveguides, biasing spring orsprings or other form of elastic members, an accelerometer, antennas andelectronic circuitry that processes measurement data as well as controlsall operations of energy conversion, propagation, and detection andwireless communications. The wireless sensing module or device can bepositioned on or within, or engaged with, or attached or affixed to orwithin, a wide range of physical systems including, but not limited toinstruments, appliances, vehicles, equipments, or other physical systemsas well as animal and human bodies, for sensing and communicatingparameters of interest in real time.

FIG. 1 is an illustration of an application of sensing insert device 100in accordance with an exemplary embodiment. The medical deviceincorporates a loop antenna 107. In this example, the medical device canintra-operatively assess a load on the prosthetic knee components(implant) and collect load data for real-time viewing of the load overvarious applied loads and angles of flexion. By way of the loop antenna107, a compact low-power energy source 117, and associated transceiverelectronics, the sensing insert device 100 can transmit measured loaddata to a receiver for permitting visualization of the level anddistribution of load at various points on the prosthetic components.This can aid the surgeon in making any adjustments needed to achieveoptimal joint balancing. The insert device 100 further includes acompact low-power energy source 117.

In general, device 100 has at least one contacting surface that couplesto the muscular-skeletal system. As shown, a first and a secondcontacting surface respectively couple to a femoral prosthetic component104 and a tibial prosthetic component 106. Device 100 is designed to beused in the normal flow of an orthopedic surgical procedure withoutspecial procedures, equipment, or components. Typically, one or morenatural components of the muscular-skeletal system are replaced whenjoint functionality substantially reduces a patient quality of life. Ajoint replacement is a common procedure in later life because it isprone to wear over time, can be damaged during physical activity, or byaccident.

A joint of the muscular-skeletal system provides movement of bones inrelation to one another that can comprise angular and rotational motion.The joint can be subjected to loading and torque throughout the range ofmotion. The joint typically comprises two bones that move in relation toone another with a low friction flexible connective tissue such ascartilage between the bones. The joint also generates a naturallubricant that works in conjunction with the cartilage to aid in ease ofmovement. Sensing insert device 100 mimics the natural structure betweenthe bones of the joint. Insert device 100 has a contacting surface onwhich a bone or a prosthetic component can moveably couple. A knee jointis disclosed for illustrative purposes but sensing insert device 100 isapplicable to other joints of the muscular-skeletal system. For example,the hip, spine, and shoulder have similar structures comprising two ormore bones that move in relation to one another. In general, insertdevice 100 can be used between two or more bones allowing movement ofthe bones during measurement or maintaining the bones in a fixedposition.

The load sensor insert device 100 and the receiver station 110 forms acommunication system for conveying data via secure wireless transmissionwithin a broadcasting range over short distances on the order of a fewmeters to protect against any form of unauthorized or accidental query.In one embodiment, the transmission range is five meters or less whichis approximately a dimension of an operating room. In practice, it canbe a shorter distance 1-2 meters to transmit to a display outside thesterile field. The transmit distance will be even shorter when device100 is used in a prosthetic implanted component. Transmission occursthrough the skin of the patient and is likely limited to less than 0.5meters. A combination of cyclic redundancy checks and a high repetitionrate of transmission during data capture permits discarding of corrupteddata without materially affecting display of data

In the illustration, a surgical procedure is performed to place afemoral prosthetic component 104 onto a prepared distal end of the femur102. Similarly, a tibial prosthetic component 106 is placed to aprepared proximal end of the tibia 108. The tibial prosthetic component106 can be a tray or plate affixed to a planarized proximal end of thetibia 108. The sensing insert device 100 is a third prosthetic componentthat is placed between the plate of the tibial prosthetic component 106and the femoral prosthetic component 104. The three prostheticcomponents enable the prostheses to emulate the functioning of a naturalknee joint. In one embodiment, sensing insert device 100 is used duringsurgery and replaced with a final insert after quantitative measurementsare taken to ensure optimal fit, balance, and loading of the prosthesis.

In one embodiment, sensing insert device 100 is a mechanical replica ofa final insert. In other words, sensing insert device 100 hassubstantially equal dimensions to the final insert. The substantiallyequal dimensions ensure that the final insert when placed in thereconstructed joint will have similar loading and balance as thatmeasured by sensing insert device 100 during the trial phase of thesurgery. Moreover, passive trial inserts are commonly used duringsurgery to determine the appropriate final insert. Thus, the procedureremains the same. It can measure loads at various points (or locations)on the femoral prosthetic component 104 and transmit the measured datato a receiving station 110 by way of an integrated loop antenna 107. Thereceiving station 110 can include data processing, storage, or display,or combination thereof and provide real time graphical representation ofthe level and distribution of the load.

As one example, the sensing insert device 100 can measure forces (Fx,Fy, and Fz) with corresponding locations and torques (e.g. Tx, Ty, andTz) on the femoral prosthetic component 104 and the tibial prostheticcomponent 106. It can then transmit this data to the receiving station110 to provide real-time visualization for assisting the surgeon inidentifying any adjustments needed to achieve optimal joint balancing.

In a further example, an external wireless energy source 125 can beplaced in proximity to the medical sensing device 100 to initiate awireless power recharging operation. As an example, the externalwireless energy source 125 generates energy transmissions that arewirelessly directed to the medical sensing device 100 and received asenergy waves via resonant inductive coupling. The external wirelessenergy source 125 can modulate a power signal generating the energytransmissions to convey downlink data that is then demodulated from theenergy waves at the medical sensing device 100. As described above, thesensing insert device 100 is a sensing insert device 100 suitable foruse in knee joint replacement surgery. The external wireless energysource 125 can be used to power the sensing insert device 100 during thesurgical procedure or thereafter when the surgery is complete and thesensing insert device 100 is implanted for long-term use. The method canalso be used to provide power and communication where the sensing insertdevice 100 is in a final insert that is part of the final prosthesisimplanted in the patient.

In one system embodiment, the sensing insert device 100 transmitsmeasured parameter data to a receiver 110 via one-way data communicationover the up-link channel for permitting visualization of the level anddistribution of the parameter at various points on the prostheticcomponents. This, combined with cyclic redundancy check error checking,provides high security and protection against any form of unauthorizedor accidental interference with a minimum of added circuitry andcomponents. This can aid the surgeon in making any adjustments needed tooptimize the installation. In addition to transmitting one-way datacommunications over the up-link channel to the receiver station 110, thesensing insert device 100 can receive downlink data from the externalwireless energy source 125 during the wireless power rechargingoperation. The downlink data can include component information, such asa serial number, or control information, for controlling operation ofthe sensing insert device 100. This data can then be uploaded to thereceiving system 110 upon request via the one-way up-link channel, ineffect providing two-way data communications over separate channels.

Separating uplink and downlink telemetry eliminates the need fortransmit-receive circuitry within the sensing insert device 100. Twounidirectional telemetry channels operating on different frequencies orwith different forms of energy enables simultaneous up and downlinktelemetry. Modulating energy emissions from the external wireless energysource 125 as a carrier for instructions achieves these benefits with aminimum of additional circuitry and components by leveraging existingcircuitry and antenna, induction loop, or piezoelectric components onthe load sensor insert device 100. The frequencies of operation of theup and downlink telemetry channels can also be selected and optimized tointerface with other devices, instruments, or equipment as needed.Separating uplink and downlink telemetry also enables addition ofdownlink telemetry without altering or upgrading existing chip-settelemetry for the one-way transmit. That is, existing chip-set telemetrycan be used for encoding and packaging data and error checking withoutmodification, yet remain communicatively coupled to the separatewireless power down-link telemetry operation for download operationsherein contemplated.

As shown, the wireless energy source 125 can include a power supply 126,a modulation circuit 127, and a data input 128. The power supply 126 canbe a battery, a charging device, a capacitor, a power connection, orother energy source for generating wireless power signals to power thesensing insert device 100. The external wireless energy source cantransmit energy in the form of, but not limited to, electromagneticinduction, or other electromagnetic or ultrasound emissions. In at leastone exemplary embodiment, the wireless energy source 125 includes a coilto electromagnetically couple with an induction coil in sensing device100 when placed in close proximity. The data input 128 can be a userinterface component (e.g., keyboard, keypad, or touchscreen) thatreceives input information (e.g., serial number, control codes) to bedownloaded to the load sensor insert device 100. The data input 128 canalso be an interface or port to receive the input information fromanother data source, such as from a computer via a wired or wirelessconnection (e.g., USB, IEEE802.16, etc.). The modulation circuitry 127can modulate the input information onto the power signals generated bythe power supply 126.

FIG. 2 is an illustration of a sensing insert device 100 placed in ajoint of the muscular-skeletal system for measuring a parameter inaccordance with an exemplary embodiment. In particular, sensing insertdevice 100 is placed in contact between a femur 102 and a tibia 108 formeasuring a parameter. In the example, a force, pressure, or load isbeing measured. The device 100 in this example can intra-operativelyassess a load on prosthetic components during the surgical procedure. Asmentioned previously, sensing insert device 100 collects data forreal-time viewing of the load forces over various applied loads andangles of flexion. It can measure the level and distribution of load atvarious points on the prosthetic component and transmit the measuredload data by way data communication to a receiver station 110 forpermitting visualization. This can aid the surgeon in making anyadjustments needed to achieve optimal joint balancing.

A proximal end of tibia 108 is prepared to receive tibial prostheticcomponent 106. Tibial prosthetic component 106 is a support structurethat is fastened to the proximal end of the tibia and is usually made ofa metal or metal alloy. The tibial prosthetic component 106 also retainsthe insert in a fixed position with respect to tibia 108. Similarly, adistal end of femur 102 is prepared to receive femoral prostheticcomponent 104. The femoral prosthetic component 104 is generally shapedto have an outer condylar articulating surface. The preparation of femur102 and tibia 108 is aligned to the mechanical axis of the leg. Thesensing insert device 100 provides a concave or flat surface againstwhich the outer condylar articulating surface of the femoral prostheticcomponent 104 rides relative to the tibia prosthetic component 106. Inparticular, the top surface of the sensing module 200 faces the condylararticulating surface of the femoral prosthetic component 104, and thebottom surface of the insert dock 202 faces the top surface of thetibial prosthetic component 106.

A final insert is subsequently fitted between femoral prostheticcomponent 104 and tibial prosthetic component 106 that has a bearingsurface that couples to femoral component 104 allowing the leg a naturalrange of motion. The final insert is has a wear surface that istypically made of a low friction polymer material. Ideally, theprosthesis has an appropriate loading, alignment, and balance thatmimics the natural leg and maximizes the life of the artificialcomponents. It should be noted that sensing module 200 can be placed afinal insert and operated similarly as disclosed herein. The sensingmodule 200 can be used to periodically monitor status of the permanentjoint.

The sensing insert device 100 is used to measure, adjust, and test thereconstructed joint prior to installing the final insert. As mentionedpreviously, the sensing insert device 100 is inserted between the femur102 and tibia 108. The condyle surface of femoral component 104 contactsa major surface of device 100. The major surface of device 100approximates a surface of a final insert. Tibial prosthetic component106 can include a cavity or tray on the major surface that receives andretains an insert dock 202 and a sensing module 200 during a measurementprocess. Each insert dock 202 has an opening to receive the sensingmodule 200. In one embodiment, the insert dock 202 can be of differentsizes and shapes but each accepts the same sensing module 200. It shouldbe noted that sensing insert device 100 is coupled to and providesmeasurement data in conjunction with other implanted prostheticcomponents. In other words, the prosthetic components are the permanentinstalled components of the patient.

Insert dock 202 is provided in different sizes and shapes. Insert dock202 can comprise many different sizes and shapes to interfaceappropriately with different manufacturer prosthetic components.Prosthetic components are made in different sizes to accommodateanatomical differences over a wide population range. Similarly, insertdock 202 is designed for different prosthetic sizes manufactured by thesame company. In at least one embodiment, multiple docks of differentdimensions are provided for a surgery. In general, the docks areselected having a major surface that fit a corresponding major surfaceof the tibial prosthetic component 106. More than one dock can beprovided each having a different height or thickness. The thickness ofthe final insert is determined by the surgical cuts to themuscular-skeletal system and measurements provided by sensing module200. The surgeon selects dock 202 based on the gap between the femur andtibial cuts. The surgeon inserts the sensing module 200 in an opening ofthe selected dock. The selected dock 202 and sensing module 200 are theninserted in the knee joint to interact with the final femoral and tibialprosthetic components. The surgeon may try two or more insert docks 202of different thicknesses (or height) before making a final decision.Each trial by the surgeon can include modifications to the joint andtissue. In one embodiment, sensing insert device 100 selected by thesurgeon has substantial equal dimensions to the final insert used. Theinsert dock 202 allows standardization on a single sensing module 200for different prosthetic platforms. Thus, the sensing module 200 iscommon to the different insert docks 202 allowing improved quality,reliability, and performance.

In one embodiment, one or more insert docks 202 are used to measure, aforce, pressure or load in one or more compartments of the knee havingthe selected predetermined height or thickness. The surgeon determinesan appropriate thickness for the final insert that yields an optimalloading and balance. In general, the absolute loading over the range ofmotion is kept within a predetermined range. The insert dock 202 andsensing module 200 can be removed from the joint if the absolute loadingis found to be above or below the predetermined range. The sensingmodule 200 is removed from the dock 202 and another selected having adifferent height. The sensing module 200 is reused and placed in thenewly selected dock 202 having a different height or thickness. The dock202 is then inserted into the knee joint. Measurements are taken todetermine if the force, pressure, or load applied by the knee is withinthe predetermined range.

Once the measurements indicate that the measured loading is within thepredetermined range, soft tissue tensioning can be used to adjust theabsolute loading. The knee balance can also be adjusted within apredetermined range if a total knee reconstruction is being performedand a sensing module 202 is used in each compartment. The position orlocation where the applied force, pressure, or loading occurs can alsobe measured by sensing module 200 allowing adjustment over the range ofmotion. Tibial prosthetic component 106 and device 100 have a combinedthickness that represents a combined thickness of tibial prostheticcomponent 106 and a final (or chronic) insert of the knee joint. Thus,the final insert thickness or depth is chosen based on the trialperformed using device 100. Typically, the final insert thickness isidentical to the device 100 to maintain the measured loading andbalance. In one embodiment, sensing module 200 and insert docks 202 aredisposed of after surgery. Alternatively, the sensing module 200 andinsert docks 202 can be cleaned, sterilized, and packaged for reuse.

The prosthesis incorporating device 100 emulates the function of anatural knee joint. Device 100 can measure loads or other parameters atvarious points throughout the range of motion. Data from device 100 istransmitted to a receiving station 110 via wired or wirelesscommunications. In one embodiment, the surgeon can view the transmittedinformation on a display. The affect of adjustments made by the surgeoncan be viewed in real time with the measurements provided by sensingmodule 200. The dock 202 and sensing module 200 is removed after themeasurements indicate that the force, pressure, or loading is correct,the knee is in balance, and the contact to the insert is centeredthroughout the range of motion. The final insert is then installed. Thefinal insert will have substantially equal dimensions as the trialinsert thereby having similar loadings, balance, and centering. In oneembodiment, the final insert includes a sensing module 200 for providingparameter measurement data on the joint throughout its useable life.

In a first embodiment, device 100 is a disposable system. Device 100 canbe disposed of after using the sensing insert device 100 to optimallyfit the joint implant. Device 100 is a low cost disposable system thatreduces capital costs, operating costs, facilitates rapid adoption ofquantitative measurement, and initiates evidentiary based orthopedicmedicine. In a second embodiment, a methodology can be put in place toclean and sterilize device 100 for reuse. In a third embodiment, device100 can be incorporated in a tool instead of being a component of thereplacement joint. The tool can be disposable or be cleaned andsterilized for reuse. In a fourth embodiment, device 100 can be apermanent component of the replacement joint. Device 100 can be used toprovide both short term and long term post-operative data on theimplanted joint. In a fifth embodiment, device 100 can be coupled to themuscular-skeletal system. In all of the embodiments, receiving station110 can include data processing, storage, or display, or combinationthereof and provide real time graphical representation of the level anddistribution of the load. Receiving station 110 can record and provideaccounting information of device 100 to an appropriate authority.

The sensing insert device 100, in one embodiment, comprises a loadsensing platform 121, an accelerometer 122, and sensing assemblies 123.This permits the sensing device 100 to assess a total load on theprosthetic components when it is being moved. The system accounts forforces due to gravity and motion. In one embodiment, load sensingplatform 121 includes two or more load bearing surfaces, at least oneenergy transducer, at least one compressible energy propagatingstructure, and at least one member for elastic support. Theaccelerometer 122 can measure acceleration. Acceleration can occur whenthe sensing device 100 is moved or put in motion. Accelerometer 122 cansense orientation, vibration, and impact. In another embodiment, thefemoral component 104 can similarly include an accelerometer 135, whichby way of a communication interface to the sensing insert device 100,can provide reference position and acceleration data to determine anexact angular relationship between the femur and tibia. The sensingassemblies 123 can reveal changes in length or compression of the energypropagating structure or structures by way of the energy transducer ortransducers. Together the load sensing platform 121, accelerometer 122(and in certain cases accelerometer 135), and sensing assemblies 123measure force or pressure external to the load sensing platform 121 ordisplacement produced by contact with the prosthetic components.

In at least one exemplary embodiment, an energy pulse is directed withinone or more waveguides in device 100 by way of pulse mode operations andpulse shaping. The waveguide is a conduit that directs the energy pulsein a predetermined direction. The energy pulse is typically confinedwithin the waveguide. In one embodiment, the waveguide comprises apolymer material. For example, urethane or polyethylene are polymerssuitable for forming a waveguide. The polymer waveguide can becompressed and has little or no hysteresis in the system. Alternatively,the energy pulse can be directed through the muscular-skeletal system.In one embodiment, the energy pulse is directed through bone of themuscular-skeletal system to measure bone density. A transit time of anenergy pulse is related to the material properties of a medium throughwhich it traverses. This relationship is used to generate accuratemeasurements of parameters such as distance, weight, strain, pressure,wear, vibration, viscosity, and density to name but a few.

Incorporating data from the accelerometer 122 with data from the othersensing components 121 and 123 assures accurate measurement of theapplied load, force, pressure, or displacement by enabling computationof adjustments to offset this external motion. This capability can berequired in situations wherein the body, instrument, appliance, vehicle,equipment, or other physical system, is itself operating or movingduring sensing of load, pressure, or displacement. This capability canalso be required in situations wherein the body, instrument, appliance,vehicle, equipment, or other physical system, is causing the portion ofthe body, instrument, appliance, vehicle, equipment, or other physicalsystem being measured to be in motion during sensing of load, pressure,or displacement.

The accelerometer 122 can operate singly, as an integrated unit with theload sensing platform 121, and/or as an integrated unit with the sensingassemblies 123. Integrating one or more accelerometers 122 within thesensing assemblages 123 to determine position, attitude, movement, oracceleration of sensing assemblages 123 enables augmentation ofpresentation of data to accurately identify, but not limited to,orientation or spatial distribution of load, force, pressure,displacement, density, or viscosity, or localized temperature bycontrolling the load and position sensing assemblages to measure theparameter or parameters of interest relative to specific orientation,alignment, direction, or position as well as movement, rotation, oracceleration along any axis or combination of axes. Measurement of theparameter or parameters of interest may also be made relative to theearth's surface and thus enable computation and presentation of spatialdistributions of the measured parameter or parameters relative to thisframe of reference.

In one embodiment, the accelerometer 122 includes direct current (DC)sensitivity to measure static gravitational pull with load and positionsensing assemblages to enable capture of, but not limited to,distributions of load, force, pressure, displacement, movement,rotation, or acceleration by controlling the sensing assemblages tomeasure the parameter or parameters of interest relative to orientationswith respect to the earths surface or center and thus enable computationand presentation of spatial distributions of the measured parameter orparameters relative to this frame of reference.

Embodiments of device 100 are broadly directed to measurement ofphysical parameters, and more particularly, to evaluating changes in thetransit time of a pulsed energy wave propagating through a medium.In-situ measurements during orthopedic joint implant surgery would be ofsubstantial benefit to verify an implant is in balance and underappropriate loading or tension. In one embodiment, the instrument issimilar to and operates familiarly with other instruments currently usedby surgeons. This will increase acceptance and reduce the adoption cyclefor a new technology. The measurements will allow the surgeon to ensurethat the implanted components are installed within predetermined rangesthat maximize the working life of the joint prosthesis and reduce costlyrevisions. Providing quantitative measurement and assessment of theprocedure using real-time data will produce results that are moreconsistent. A further issue is that there is little or no implant datagenerated from the implant surgery, post-operatively, and long term.Device 100 can provide implant status data to the orthopedicmanufacturers and surgeons. Moreover, data generated by directmeasurement of the implanted joint itself would greatly improve theknowledge of implanted joint operation and joint wear thereby leading toimproved design and materials.

As mentioned previously, device 100 can be used for other jointsurgeries; it is not limited to knee replacement implant or implants.Moreover, device 100 is not limited to trial measurements. Device 100can be incorporated into the final joint system to provide datapost-operatively to determine if the implanted joint is functioningcorrectly. Early determination of a problem using device 100 can reducecatastrophic failure of the joint by bringing awareness to a problemthat the patient cannot detect. The problem can often be rectified witha minimal invasive procedure at lower cost and stress to the patient.Similarly, longer term monitoring of the joint can determine wear ormisalignment that if detected early can be adjusted for optimal life orreplacement of a wear surface with minimal surgery thereby extending thelife of the implant. In general, device 100 can be shaped such that itcan be placed or engaged or affixed to or within load bearing surfacesused in many orthopedic applications (or used in any orthopedicapplication) related to the musculoskeletal system, joints, and toolsassociated therewith. Device 100 can provide information on acombination of one or more performance parameters of interest such aswear, stress, kinematics, kinetics, fixation strength, ligament balance,anatomical fit and balance.

FIG. 3 is a perspective view of a medical sensing platform comprising anencapsulating enclosure in accordance with one embodiment. In general,parameters of the muscular-skeletal system can be measured with asensing module 200 that in one embodiment is an integral part of acomplete sensing insert device 100. The sensing module 200 is aself-contained sensor within an encapsulating enclosure that integratessensing assemblages, an electronic assemblage that couples to thesensing assemblages, a power source, signal processing, and wirelesscommunication. All components required for the measurement are containedin the sensing module 200. The sensing module 200 has at least onecontacting surface for coupling to the muscular-skeletal system. Aparameter of the muscular-skeletal system is applied to the contactsurfaces to be measured by the one or more sensing assemblages therein.As will be disclosed in further detail herein, the sensing module 200 ispart of a system that allows intra-operative and post-operative sensingof a joint of the muscular-skeletal system. More specifically, sensingmodule 200 is placed within a temporary or permanent prostheticcomponent that has a similar form factor as the passive prostheticcomponent currently being used. This has a benefit of rapid adoptionbecause the sensing platform is inserted identically to the commonlyused passive component but can provide much needed quantitativemeasurements with little or no procedural changes.

As shown, the sensing insert device 100 comprises an insert dock 202 andthe sensing module 200. Sensing insert device 100 is a non-permanent ortemporary measurement device that is used intra-operatively to providequantitative data related to the installation of prosthetic componentssuch as in joint replacement surgery. The combination of the insert dock202 and sensing module 202 has a form factor substantially equal to afinal insert device. The final insert device can be a passive componentor sensored incorporating sensing module 200. The substantially equalform factor of sensing insert device 100 results in no extraneousstructures in the surgical field that can interfere with the procedure.For example, a final insert device is designed to mimic the function ofthe natural component it is replacing. The final insert device allowsnatural movement of the muscular-skeletal system and does not interferewith ligaments, tendons, tissue, muscles, and other components of themuscular-skeletal system. Similarly, sensing insert device 100 allowsexposure of the surgical field around the joint by having the similarform factor as the final insert thereby allowing the surgeon to makeadjustments during the installation in a natural setting withquantitative measurements to support the modifications.

In one embodiment, insert dock 202 is an adaptor. Insert dock 202 ismade in different sizes. In general, prosthetic components aremanufactured in different sizes to accommodate variation in themuscular-skeletal system from person to person. In the example, the sizeof insert dock 202 is chosen to mate with the selected prostheticimplant components. In particular, a feature 204 aligns with and retainsinsert dock 202 in a fixed position to a prosthetic or natural componentof the muscular-skeletal system. The insert dock 202 is a passivecomponent having an opening for receiving sensing module 200. Theopening is positioned to place the contacting surfaces in a properorientation to measure the parameter when used in conjunction with otherprosthetic components. The insert dock 202 as an adaptor can bemanufactured at low cost. Moreover, insert dock 202 can be formed foradapting to different prosthetic manufacturers thereby increasing systemflexibility. This allows a standard sensing module 200 to be providedbut customized for appropriate size and dimensions through dock 202 forthe specific application and manufacturer component.

The one or more sensing assemblages within sensing module 200 couple tothe contacting surfaces of sensing module 200 for receiving the appliedparameter of the muscular-skeletal system. In one embodiment, a sensingassemblage comprises one or more energy transducers coupled to anelastic structure. The elastic structure allows the propagation ofenergy waves. The forms of energy propagated through the elastic energypropagating structures may include, but is not limited to, sound,ultrasound, or electromagnetic radiation including radio frequency,infrared, or light. A change in the parameter applied to the contactingsurfaces results in a change a dimension of the elastic structure. Thedimension of the elastic structure can be measured precisely usingcontinuous wave, pulsed, or pulsed echo measurement. The dimension andmaterial properties of the elastic structure have a known relationshipto the parameter being measured. Thus, the dimension is preciselymeasured and converted to the parameter. Other factors such as movementor acceleration can be taken into account in the calculation. As anexample, a force, pressure, or load applied to the one or morecontacting surfaces of sensing module 200 is used to illustrate aparameter measurement hereinbelow. It should be noted that this is forillustration purposes and that the sensing module 200 can be used tomeasure other parameters.

As will be shown ahead, the encapsulating enclosure can serve in a firstembodiment as a trial implant for orthopedic surgical procedures,namely, for determining load forces on prosthetic components and themusculoskeletal system. In a second embodiment, the encapsulatingenclosure can be placed within a permanent prosthetic component for longterm monitoring. The encapsulating enclosure supports and protectsinternal mechanical and electronic components from external physical,mechanical, chemical, and electrical, and electromagnetic intrusion thatmight compromise sensing or communication operations of the module ordevice. The integration of the internal components is designed tominimize adverse physical, mechanical, electrical, and ultrasonicinteractions that might compromise sensing or communication operationsof the module or device.

FIG. 4 is a perspective view of a medical sensing device suitable foruse as a bi-compartmental implant and comprising an encapsulatingenclosure in accordance with one embodiment. As shown, the sensinginsert device 100 comprises two sensing modules 200. Each sensing module200 is a self-contained encapsulated enclosure that can make individualor coordinated parameter measurements. For example, the sensing insertdevice 100 can be used to assess load forces on a bi-compartmental kneejoint implant. In particular, both sensing modules 200 can individually,or in combination, report applied loading forces. Bi-compartmentalsensing provides the benefit of providing quantitative measurement tobalance each compartment in relation to one another.

Similar to that described above, insert dock 202 is an adaptor havingtwo openings instead of one. Insert dock 202 can be made in differentsizes to accommodated different sized prosthetic components anddifferent manufacturers. The insert dock 202 with two openings is apassive component for receiving two separate sensing modules 200. Theopening is positioned to place the contacting surfaces in a properorientation to measure the parameter when used in conjunction with otherprosthetic components. In general, encapsulated enclosures can bepositioned on or within, or engaged with, or attached or affixed to orwithin, a wide range of physical systems including, but not limited toinstruments, appliances, vehicles, equipments, or other physical systemsas well as animal and human bodies, for sensing and communicating theparameter or parameters of interest in real time. Similar to thatdescribed above, insert dock 202 as an adaptor can be manufactured atlow cost providing design flexibility and allowing rapid adoption ofquantitative measurement.

FIG. 5 is an exemplary block diagram of the components of the sensingmodule 200 in accordance with an exemplary embodiment. It should benoted that the sensing module could comprise more or less than thenumber of components shown. As illustrated, the sensing module includesone or more sensing assemblages 303, a transceiver 320, an energystorage 330, electronic circuitry 307, one or more mechanical supports315 (e.g., springs), and an accelerometer 302. In the non-limitingexample, an applied compressive force can be measured by the sensingmodule.

The sensing assemblage 303 can be positioned, engaged, attached, oraffixed to the contact surfaces 306. Mechanical supports 315 serve toprovide proper balancing of contact surfaces 306. In at least oneexemplary embodiment, contact surfaces 306 are load-bearing surfaces. Ingeneral, the propagation structure 305 is subject to the parameter beingmeasured. Surfaces 306 can move and tilt with changes in applied load;actions which can be transferred to the sensing assemblages 303 andmeasured by the electronic circuitry 307. The electronic circuitry 307measures physical changes in the sensing assemblage 303 to determineparameters of interest, for example a level, distribution and directionof forces acting on the contact surfaces 306. In general, the sensingmodule is powered by the energy storage 330.

As one example, the sensing assemblage 303 can comprise an elastic orcompressible propagation structure 305 between a transducer 304 and atransducer 314. In the current example, transducer 304 can be anultrasound (or ultrasonic) resonator, and the elastic or compressiblepropagation structure 305 can be an ultrasound (or ultrasonic) waveguide(or waveguides). The electronic circuitry 307 is electrically coupled tothe sensing assemblages 303 and translates changes in the length (orcompression or extension) of the sensing assemblages 303 to parametersof interest, such as force. It measures a change in the length of thepropagation structure 305 (e.g., waveguide) responsive to an appliedforce and converts this change into electrical signals which can betransmitted via the transceiver 320 to convey a level and a direction ofthe applied force. In other arrangements herein contemplated, thesensing assemblage 303 may require only a single transducer. In yetother arrangements, the sensing assemblage 303 can includepiezoelectric, capacitive, optical or temperature sensors or transducersto measure the compression or displacement. It is not limited toultrasonic transducers and waveguides.

The accelerometer 302 can measure acceleration and static gravitationalpull. Accelerometer 302 can be single-axis and multi-axis accelerometerstructures that detect magnitude and direction of the acceleration as avector quantity. Accelerometer 302 can also be used to senseorientation, vibration, impact and shock. The electronic circuitry 307in conjunction with the accelerometer 302 and sensing assemblies 303 canmeasure parameters of interest (e.g., distributions of load, force,pressure, displacement, movement, rotation, torque and acceleration)relative to orientations of the sensing module with respect to areference point. In such an arrangement, spatial distributions of themeasured parameters relative to a chosen frame of reference can becomputed and presented for real-time display.

The transceiver 320 comprises a transmitter 309 and an antenna 310 topermit wireless operation and telemetry functions. In variousembodiments, the antenna 310 can be configured by design as anintegrated loop antenna. As will be explained ahead, the integrated loopantenna is configured at various layers and locations on the electronicsubstrate with electrical components and by way of electronic controlcircuitry to conduct efficiently at low power levels. Once initiated thetransceiver 320 can broadcast the parameters of interest in real-time.The telemetry data can be received and decoded with various receivers,or with a custom receiver. The wireless operation can eliminatedistortion of, or limitations on, measurements caused by the potentialfor physical interference by, or limitations imposed by, wiring andcables connecting the sensing module with a power source or withassociated data collection, storage, display equipment, and dataprocessing equipment.

The transceiver 320 receives power from the energy storage 330 and canoperate at low power over various radio frequencies by way of efficientpower management schemes, for example, incorporated within theelectronic circuitry 307. As one example, the transceiver 320 cantransmit data at selected frequencies in a chosen mode of emission byway of the antenna 310. The selected frequencies can include, but arenot limited to, ISM bands recognized in International TelecommunicationUnion regions 1, 2 and 3. A chosen mode of emission can be, but is notlimited to, Gaussian Frequency Shift Keying, (GFSK), Amplitude ShiftKeying (ASK), Phase Shift Keying (PSK), Minimum Shift Keying (MSK),Frequency Modulation (FM), Amplitude Modulation (AM), or other versionsof frequency or amplitude modulation (e.g., binary, coherent,quadrature, etc.).

The antenna 310 can be integrated with components of the sensing moduleto provide the radio frequency transmission. The substrate for theantenna 310 and electrical connections with the electronic circuitry 307can further include a matching network. This level of integration of theantenna and electronics enables reductions in the size and cost ofwireless equipment. Potential applications may include, but are notlimited to any type of short-range handheld, wearable, or other portablecommunication equipment where compact antennas are commonly used. Thisincludes disposable modules or devices as well as reusable modules ordevices and modules or devices for long-term use.

The energy storage 330 provides power to electronic components of thesensing module. It can be charged by wired energy transfer,short-distance wireless energy transfer or a combination thereof.External power sources can include, but are not limited to, a battery orbatteries, an alternating current power supply, a radio frequencyreceiver, an electromagnetic induction coil, a photoelectric cell orcells, a thermocouple or thermocouples, or an ultrasound transducer ortransducers. By way of the energy storage 330, the sensing module can beoperated with a single charge until the internal energy is drained. Itcan be recharged periodically to enable continuous operation. The energystorage 330 can utilize power management technologies such asreplaceable batteries, supply regulation technologies, and chargingsystem technologies for supplying energy to the components of thesensing module to facilitate wireless applications.

The energy storage 330 minimizes additional sources of energy radiationrequired to power the sensing module during measurement operations. Inone embodiment, as illustrated, the energy storage 330 can include acapacitive energy storage device 308 and an induction coil 311. Externalsource of charging power can be coupled wirelessly to the capacitiveenergy storage device 308 through the electromagnetic induction coil orcoils 311 by way of inductive charging. The charging operation can becontrolled by power management systems designed into, or with, theelectronic circuitry 307. As one example, during operation of electroniccircuitry 307, power can be transferred from capacitive energy storagedevice 308 by way of efficient step-up and step-down voltage conversioncircuitry. This conserves operating power of circuit blocks at a minimumvoltage level to support the required level of performance.

In one configuration, the energy storage 330 can further serve tocommunicate downlink data to the transceiver 320 during a rechargingoperation. For instance, downlink control data can be modulated onto theenergy source signal and thereafter demodulated from the induction coil311 by way of electronic control circuitry 307. This can serve as a moreefficient way for receiving downlink data instead of configuring thetransceiver 320 for both uplink and downlink operation. As one example,downlink data can include updated control parameters that the sensingmodule uses when making a measurement, such as external positionalinformation, or for recalibration purposes, such as spring biasing. Itcan also be used to download a serial number or other identificationdata.

The electronic circuitry 307 manages and controls various operations ofthe components of the sensing module, such as sensing, power management,telemetry, and acceleration sensing. It can include analog circuits,digital circuits, integrated circuits, discrete components, or anycombination thereof. In one arrangement, it can be partitioned amongintegrated circuits and discrete components to minimize powerconsumption without compromising performance. Partitioning functionsbetween digital and analog circuit enhances design flexibility andfacilitates minimizing power consumption without sacrificingfunctionality or performance. Accordingly, the electronic circuitry 307can comprise one or more Application Specific Integrated Circuit (ASIC)chips, for example, specific to a core signal processing algorithm.

In another arrangement, the electronic circuitry can comprise acontroller such as a programmable processor, a Digital Signal Processor(DSP), a microcontroller, or a microprocessor, with associated storagememory and logic. The controller can utilize computing technologies withassociated storage memory such a Flash, ROM, RAM, SRAM, DRAM or otherlike technologies for controlling operations of the aforementionedcomponents of the sensing module. In one arrangement, the storage memorymay store one or more sets of instructions (e.g., software) embodyingany one or more of the methodologies or functions described herein. Theinstructions may also reside, completely or at least partially, withinother memory, and/or a processor during execution thereof by anotherprocessor or computer system.

The electronics assemblage also supports testability and calibrationfeatures that assure the quality, accuracy, and reliability of thecompleted wireless sensing module or device. A temporary bi-directionalinterconnect assures a high level of electrical observability andcontrollability of the electronics. The test interconnect also providesa high level of electrical observability of the sensing subsystem,including the transducers, waveguides, and mechanical spring or elasticassembly. Carriers or fixtures emulate the final enclosure of thecompleted wireless sensing module or device during manufacturingprocessing thus enabling capture of accurate calibration data for thecalibrated parameters of the finished wireless sensing module or device.These calibration parameters are stored within the on-board memoryintegrated into the electronics assemblage.

Applications for sensing module 200 may include, but are not limited to,disposable modules or devices as well as reusable modules or devices andmodules or devices for long-term use. In addition to non-medicalapplications, examples of a wide range of potential medical applicationsmay include, but are not limited to, implantable devices, modules withinimplantable devices, intra-operative implants or modules withinintra-operative implants or trial inserts, modules within inserted oringested devices, modules within wearable devices, modules withinhandheld devices, modules within instruments, appliances, equipment, oraccessories of all of these, or disposables within implants, trialinserts, inserted or ingested devices, wearable devices, handhelddevices, instruments, appliances, equipment, or accessories to thesedevices, instruments, appliances, or equipment.

FIG. 6 is a diagram of an exemplary communications system 400 forshort-range telemetry according to one embodiment. As illustrated, theexemplary communications system 400 comprises medical devicecommunications components 410 of the sensing insert device 100 (seeFIG. 1) and receiving system communications components 450 of thereceiving system 110 (see FIG. 1). The medical device communicationscomponents 410 are inter-operatively coupled to include, but not limitedto, the antenna 412, a matching network 414, the telemetry transceiver416, a CRC circuit 418, a data packetizer 422, a data input 424, a powersource 426, and an application specific integrated circuit (ASIC) 420.The medical device communications components 410 may include more orless than the number of components shown and are not limited to thoseshown or the order of the components.

The receiving station communications components 450 comprise an antenna452, the matching network 454, the telemetry receiver 456, the CRCcircuit 458, the data packetizer 460, and optionally a USB interface462. Notably, other interface systems can be directly coupled to thedata packetizer 460 for processing and rendering sensor data.

With respect to FIG. 1, in view of the communication components of FIG.6, the sensing insert device 100 acquires sensor data by way of the datainput to the ASIC 420. Referring briefly to FIG. 5, the ASIC 420 isoperatively coupled to sensing assemblies 303. In one embodiment, achange in the parameter being measured by device 100 produces a changein a length of a compressible propagation structure 305. ASIC 420controls the emission of energy waves into propagation structure 305 andthe detection of propagated energy waves. ASIC 420 generates datarelated to transit time, frequency, or phase of propagated energy waves.The data corresponds to the length of propagation structure 305, whichcan be translated to the parameter of interest by way of a knownfunction or relationship. Similarly, the data can comprise voltage orcurrent measurements from a MEMS structure, piezo-resistive sensor,strain gauge, or other sensor type that is used to measure theparameter. The data packetizer 422 assembles the sensor data intopackets; this includes sensor information received or processed by ASIC420. The ASIC 420 can comprise specific modules for efficientlyperforming core signal processing functions of the medical devicecommunications components 410. The ASIC 420 provides the further benefitof reducing the form factor of sensing insert device 100 to meetdimensional requirements for integration into temporary or permanentprosthetic components.

The CRC circuit 418 applies error code detection on the packet data. Thecyclic redundancy check is based on an algorithm that computes achecksum for a data stream or packet of any length. These checksums canbe used to detect interference or accidental alteration of data duringtransmission. Cyclic redundancy checks are especially good at detectingerrors caused by electrical noise and therefore enable robust protectionagainst improper processing of corrupted data in environments havinghigh levels of electromagnetic activity. The telemetry transmitter 416then transmits the CRC encoded data packet through the matching network414 by way of the antenna 412. The matching networks 414 and 454 providean impedance match for achieving optimal communication power efficiency.

The receiving system communications components 450 receive transmissionsent by medical device communications components 410. In one embodiment,telemetry transmitter 416 is operated in conjunction with a dedicatedtelemetry receiver 456 that is constrained to receive a data streambroadcast on the specified frequencies in the specified mode ofemission. The telemetry receiver 456 by way of the receiving stationantenna 452 detects incoming transmissions at the specified frequencies.The antenna 452 can be a directional antenna that is directed to adirectional antenna of components 410. Using at least one directionalantenna can reduce data corruption while increasing data security byfurther limiting where the data is radiated. A matching network 454couples to antenna 452 to provide an impedance match that efficientlytransfers the signal from antenna 452 to telemetry receiver 456.Telemetry receiver 456 can reduce a carrier frequency in one or moresteps and strip off the information or data sent by components 410.Telemetry receiver 456 couples to CRC circuit 458. CRC circuit 458verifies the cyclic redundancy checksum for individual packets of data.CRC circuit 458 is coupled to data packetizer 460. Data packetizer 460processes the individual packets of data. In general, the data that isverified by the CRC circuit 458 is decoded (e.g., unpacked) andforwarded to an external data processing device, such as an externalcomputer, for subsequent processing, display, or storage or somecombination of these.

The telemetry receiver 456 is designed and constructed to operate onvery low power such as, but not limited to, the power available from thepowered USB port 462, or a battery. In another embodiment, the telemetryreceiver 456 is designed for use with a minimum of controllablefunctions to limit opportunities for inadvertent corruption or malicioustampering with received data. The telemetry receiver 456 can be designedand constructed to be compact, inexpensive, and easily manufactured withstandard manufacturing processes while assuring consistently high levelsof quality and reliability.

In one configuration, the communication system 400 operates in atransmit-only operation with a broadcasting range on the order of a fewmeters to provide high security and protection against any form ofunauthorized or accidental query. The transmission range can becontrolled by the transmitted signal strength, antenna selection, or acombination of both. A high repetition rate of transmission can be usedin conjunction with the Cyclic Redundancy Check (CRC) bits embedded inthe transmitted packets of data during data capture operations therebyenabling the receiving system 110 to discard corrupted data withoutmaterially affecting display of data or integrity of visualrepresentation of data, including but not limited to measurements ofload, force, pressure, displacement, flexion, attitude, and positionwithin operating or static physical systems.

By limiting the operating range to distances on the order of a fewmeters the telemetry transmitter 416 can be operated at very low powerin the appropriate emission mode or modes for the chosen operatingfrequencies without compromising the repetition rate of the transmissionof data. This mode of operation also supports operation with compactantennas, such as an integrated loop antenna. The combination of lowpower and compact antennas enables the construction of, but is notlimited to, highly compact telemetry transmitters that can be used for awide range of non-medical and medical applications. Examples ofpotential medical applications may include, but are not limited to,implantable devices, modules within implantable devices, intra-operativeimplants or modules within intra-operative implants or trial inserts,modules within inserted or ingested devices, modules within wearabledevices, modules within handheld devices, modules within instruments,appliances, equipment, or accessories of all of these, or disposableswithin implants, trial inserts, inserted or ingested devices, wearabledevices, handheld devices, instruments, appliances, equipment, oraccessories to these devices, instruments, appliances, or equipment.

The transmitter security as well as integrity of the transmitted data isassured by operating the telemetry system within predeterminedconditions. The security of the transmitter cannot be compromisedbecause it is operated in a transmit-only mode and there is no pathwayto hack into medical device communications components 410. The integrityof the data is assured with the use of the CRC algorithm and therepetition rate of the measurements. The risk of unauthorized receptionof the data is minimized by the limited broadcast range of the device.Even if unauthorized reception of the data packets should occur thereare counter measures in place that further mitigate data access. A firstmeasure is that the transmitted data packets contain only binary bitsfrom a counter along with the CRC bits. A second measure is that no datais available or required to interpret the significance of the binaryvalue broadcast at any time. A third measure that can be implemented isthat no patient or device identification data is broadcast at any time.

The telemetry transmitter 416 can also operate in accordance with someFCC regulations. According to section 18.301 of the FCC regulations theISM bands within the USA include 6.78, 13.56, 27.12, 30.68, 915, 2450,and 5800 MHz as well as 24.125, 61.25, 122.50, and 245 GHz. Globallyother ISM bands, including 433 MHz, are defined by the InternationalTelecommunications Union in some geographic locations. The list ofprohibited frequency bands defined in 18.303 are “the following safety,search and rescue frequency bands is prohibited: 490-510 kHz, 2170-2194kHz, 8354-8374 kHz, 121.4-121.6 MHz, 156.7-156.9 MHz, and 242.8-243.2MHz.” Section 18.305 stipulates the field strength and emission levelsISM equipment must not exceed when operated outside defined ISM bands.In summary, it may be concluded that ISM equipment may be operatedworldwide within ISM bands as well as within most other frequency bandsabove 9 KHz given that the limits on field strengths and emission levelsspecified in section 18.305 are maintained by design or by activecontrol. As an alternative, commercially available ISM transceivers,including commercially available integrated circuit ISM transceivers,may be designed to fulfill these field strengths and emission levelrequirements when used properly.

In one configuration, the telemetry transmitter 416 can also operate inunlicensed ISM bands or in unlicensed operation of low power equipment,wherein the ISM equipment (e.g., telemetry transmitter 416) may beoperated on ANY frequency above 9 kHz except as indicated in Section18.303 of the FCC code.

Wireless operation eliminates distortion of, or limitations on,measurements caused by the potential for physical interference by, orlimitations imposed by, wiring and cables connecting the wirelesssensing module or device with a power source or with data collection,storage, or display equipment. Power for the sensing components andelectronic circuits is maintained within the wireless sensing module ordevice on an internal energy storage device. This energy storage deviceis charged with external power sources including, but not limited to, abattery or batteries, super capacitors, capacitors, an alternatingcurrent power supply, a radio frequency receiver, an electromagneticinduction coil, a photoelectric cell or cells, a thermocouple orthermocouples, or an ultrasound transducer or transducers. The wirelesssensing module may be operated with a single charge until the internalenergy source is drained or the energy source may be rechargedperiodically to enable continuous operation. The embedded power supplyminimizes additional sources of energy radiation required to power thewireless sensing module or device during measurement operations.Telemetry functions are also integrated within the wireless sensingmodule or device. Once initiated the telemetry transmitter continuouslybroadcasts measurement data in real time. Telemetry data may be receivedand decoded with commercial receivers or with a simple, low cost customreceiver.

A method can be practiced with more or less than the number of stepsshown and is not limited to the order shown. To describe the method,reference will be made to the components of FIG. 5, although it isunderstood that the method can be implemented in any other manner usingother suitable components. Generally, method is directed to non-secureapplications for one-way transmission communications, for example, wherean implanted medical device or sensor transmits data to a receivingstation (e.g., 110 see FIG. 1) but does not receive confirmation fromthe receiving station, although in various embodiments, the implantedmedical device includes an integrated receiver for receivingconfirmation and acknowledgement communications.

The method can start in a state wherein the sensing insert device 100has been inserted and powered on, for example, within a knee prosthesisimplant. The medical device can be powered on via manual intervention,for example, by the surgeon or technician implanting the medical deviceduring a surgical procedure, or the device can turn on automaticallyafter a duration of time or at certain time intervals, for example, 1hour after manual activation, or every 10 seconds after power up,depending on an operating mode.

In a first step, the medical device acquires sensor data such as loadinformation (e.g., force, location, duration, etc.) from the sensingmodule 200. The electronic circuitry 307 generates the load data by wayof the sensing assemblies 303, for instance, by converting changes inlength of ultrasonic propagation structures (waveguides) to force data.In a second step, the sensing module 200 evaluates data bounds on theload data. In a third step, sensing module 200 assigns priorities basedon the data bounds. Sensor data outside a predetermined range or above apredefined threshold can be flagged with a priority or discarded. Forexample, sensor data that falls outside a safe range or exceeds a safelevel (e.g., applied force level, angle of flexion, excessive rotation)is prioritized accordingly.

In a fourth step, the sensing module 200 generates a packet of dataincluding the sensor data, priority, and any corresponding information.In a fifth step, the sensing module 200 determines its communicationsmode based on operating mode and priority level. The operating modeindicates whether the sensing module 200 is operating in a power savingmode (e.g., standby) or other power management mode and takes intoaccount information such as remaining battery life and drain. In a sixthstep, a Cyclic Redundancy Check (CRC) can be appended to the datapacked. In other embodiments, more sophisticated forward errorcorrection schemes (e.g., block coding, convolutional coding) can beapplied along with secure encryption or key-exchange cryptographicprotocols.

The cyclic redundancy check (CRC) is a non-secure form of message digestdesigned to detect accidental changes to raw computer data. The CRC stepcomprises calculating a short, fixed-length sequence, known as the CRCcode, for each block of data and sends or stores them both together.When a block is read or received the receiving station 110 (FIG. 1)repeats the calculation; if the new CRC does not match the one sent (orin some cases, cancel it out) then the block contains a data error andthe receiving station 110 may take corrective action such as rereadingor requesting the block be sent again. Briefly, FIG. 13, illustrates anexemplary data packet 1300 containing sensor data (e.g., Fx, duration,location), a priority level (e.g., 1 to 10), and a CRC.

In a seventh step, the transceiver 320 then transmits the data packetbased on the priority level and operating mode. For instance, a lowpriority data packet can be appended with previous low-priority datapackets and then transmitted over a single communication channel as adata stream, or at staggered time intervals to conserve power (e.g.,scheduled to transmit every 10 seconds). The bundled packet data canthen be decoded at the receiving station 110 and thereafter processedaccordingly. Alternatively, a high priority packet can be transmittedimmediately instead of a delayed time or the scheduled transmitintervals. Depending on the communication mode (e.g., priority level,operating mode), the transceiver may transmit the same high prioritypacket multiple times in a redundant manner to guarantee receipt. Thisensures that the data is received and processed at the receiving station110 in the event an immediate course of action or response is necessary,for example, to ensure the patient's safety or to report a warning.

The sensor data can be transmitted at the selected frequencies in thechosen mode of emission by way of the antenna 310. In certainconfigurations, the antenna 310 is an integrated loop antenna designedinto a substrate of the sensing module 200 for maximizing powerefficiency. As an example the chosen frequencies can include, but arenot limited to, ISM bands recognized in International TelecommunicationUnion regions 1, 2, and 3 and the chosen mode of emission may be, but isnot limited to, Gaussian Frequency Shift Keying, (GFSK) or othersversion of frequency or amplitude shift keying or modulation.

The receiving station 110 (see FIG. 1) 110 receives packets of databroadcast in the specified mode of emission on the specified frequenciesand verifies the cyclic redundancy check checksum for individual packetsof data or bundled packet data. Data that cannot be verified may bediscarded. Data that are verified are forward to an external dataprocessing device, such as an external computer, for subsequentprocessing, display, or storage or combination thereof.

FIG. 7 is an illustration of a block model diagram 500 of the sensingmodule 200 in accordance with an exemplary embodiment. In particular,the diagram 500 shows where certain components are replaced orsupplemented with one or more Application Specific Integrated Circuits(ASICs). Referring briefly to FIG. 5, electronic circuitry 307 iscoupled to the one or more sensing assemblages and includes circuitrythat can control sensor operations. Electronic circuitry 307 includesmultiple channels that can operate more than one device. Sensing module200 is optimized to operate under severe power constraints. Electroniccircuitry 307 includes power management circuitry that controls powerup, power down, and minimizes power usage through the control ofindividual blocks. The architecture is designed to enable only blocksrequired for the current operation.

Referring back to FIG. 7, the ASIC provides significant benefit inreducing power requirements allowing the module 200 to be powered by atemporary power source such as a super capacitor or capacitor. The ASICand super capacitor have a small form factor allowing module 200 to beintegrated within a temporary or permanent prosthetic component. Module200 incorporates one or more sensors comprising at least one transducerand a compressible media, the operation of which is disclosed in detailherein. As shown, a sensing assemblage comprises a transducer 502,compressible propagation structure 504, and a transducer 506. It shouldbe noted that other sensors such as MEMS devices, strain gauges, andpiezo-resistive sensors can be used with the ASIC. In particular, theASIC incorporates A/D and D/A circuitry (not shown) to digitize currentand voltage output from these types of sensing components. Transducers502 and 506 operatively couple to compressible propagation structure504. In a non-limiting example, transducer 506 to emits energy wavesinto compressible structure 504 while transducer 502 detects propagatedenergy waves. Compressible propagation structure 504 is coupled to aload bearing or contacting surface 508 and an encapsulating enclosure510 of sensing module 200. A parameter to be measured is applied toeither contacting surface 508, encapsulating enclosure 510, or both. Inone embodiment, springs 560 couple to contacting surface 508 andencapsulating enclosure 510 to support compressible propagationstructure 504. In particular, springs 560 prevent cantilevering ofcontacting surface 508, reduce hysteresis caused by material propertiesof compressible propagation structure 504, and improve sensor responsetime to changes in the applied parameter.

In one embodiment, a first ASIC includes a charging circuit 514 andpower management circuitry 518. The power management circuitry 518couples to the charging circuit, other blocks of the ASIC and externalcomponents/circuitry to minimize power consumption of the integratedcircuit. The charging circuit 514 operatively couples to an inductioncoil 512 and energy storage 516. In a non-limiting example, inductioncoil 512 couples to an external coil that provides energy to chargeenergy storage 516. Induction coil 512 and the external coil are placedin proximity to each other thereby electro-magnetically coupling to oneanother. Induction coil 512 is coupled to energy storage 516. Chargingcircuit 514 controls the charging of energy storage 516. Chargingcircuit 514 can determine when charging is complete, monitor poweravailable, and regulate a voltage provided to the operational circuitry.Charging circuit 514 can charge a battery in sensing module 200.Alternatively, a capacitor or super capacitor can be used to power thefirst ASIC for a time sufficient to acquire the desired measurements. Acapacitor has the benefit of a long or indefinite shelf life and fastcharge time. In either charging scenario, energy from the external coilis coupled to the induction coil 512. The energy from induction coil 512is then stored in a medium such as a battery or capacitor.

Benefits of ultracapacitors, ultra capacitors, or super capacitors, orother form of capacitors as a power source instead or, or in conjunctionwith, other power sources or rechargeable technologies include, but arenot limited to, enabling a high level of miniaturization asultracapacitors, ultra capacitors, or super capacitors are smaller thansmallest available battery for the same level of energy and power formany low power applications or applications that require power onlyintermittently or as a short-term backup for other power sources.

For applications that require power only intermittently, capacitorsenable rapid recharge that is much faster than battery technologies andrechargeable chemistries regardless of their energy capacity. A chargetime, from a completely uncharged state takes minutes because nochemical processes are involved in charging capacitors. This may becompared to charge times on the order of hours for many batterytechnologies that cannot be charged at a rate faster that one-half theenergy storage capacity of the battery within one hour. In practice,many battery applications charge at a much slower rate. Many capacitorshave the added benefit of almost indefinite lifetimes. There is nodeterioration of a capacitor's storage capacity when uncharged,regardless of length of time at zero charge. Another benefit is thatovercharging capacitors may pose less risk to electronics within anelectronic module or device than overcharging batteries might pose.Furthermore, capacitors eliminate storage and disposal limitations ofbatteries with no risk of chemical leakage. In addition, capacitors canhave a smaller form factor, are surface-mountable, and integrate wellinto the electronics assemblies and standard surface-mount electronicassembly processes.

Use capacitors to provide operating power for wireless devices,telemetry devices, or medical devices provides design, construction, andoperating flexibility over a wide range of potential applications.Capacitors can be charged by connecting them to other power sources suchas, but not limited to, a battery or batteries, an alternating current(AC) power supply, a radio frequency (RF) receiver, or anelectromagnetic induction coil or coils, a photoelectric cell or cells,a thermocouple or thermocouples, capacitors, or an ultrasound transduceror transducers. For compact electronic modules or devices,ultracapacitors, super capacitors, or other form of capacitors providemany benefits over other rechargeable technologies.

The first ASIC further includes circuitry to operate and capture datafrom the sensing assemblages. A parameter to be measured is applied tocompressible propagation structure 504. As an example of parametermeasurement, a force, pressure, or load is applied across contactingsurface 508 and encapsulating enclosure 510. The force, pressure, orload affects the length of the compressible propagation structure 504.The circuitry on the first ASIC forms a positive closed loop feedbackcircuit that maintains the emission, propagation, and detection ofenergy waves in the compressible propagation structure 504. The firstASIC operatively couples to transducers 502 and 506 to control thepositive closed loop feedback circuit that is herein called apropagation tuned oscillator (PTO). The first ASIC measures a transittime, frequency, or phase of propagated energy waves. The measurement isused to determine the length of compressible propagation structure 504.The energy waves emitted into compressible propagation structure 504 canbe continuous or pulsed. The energy waves can propagate by a direct pathor be reflected.

The first ASIC comprises an oscillator 520, a switch 522, driver 524,matching network 526, MUX 528, and control circuit 536. The oscillator520 is used as a reference clock for the ASIC and enables the PTO tobegin emission of energy waves into the compressible propagationstructure 504. Oscillator 520 in the first ASIC can be coupled to anexternal component such as a crystal oscillator to define and provide astable frequency of operation. Switch 522 couples the oscillator 520 toMUX 528. Control circuit 536 operatively enables MUX 528 and switch 522to couple oscillator 520 to driver 524 during a startup sequence. Driver524 and matching network 526 couple to transducer 506. Driver 524 drivestransducer 506 to emit an energy wave. Matching network 526 impedancematches driver 524 to the transducer 506 to reduce power consumptionduring energy wave emission.

In one embodiment, transducer 506 emits one or more energy waves intothe compressible propagation structure 504 at a first location.Transducer 506 is located at a second location of compressiblepropagation structure 504. Transducer 506 detects propagated energywaves at the second location and generates a signal corresponding to thepropagated energy waves. The first ASIC further comprises a MUX 530,pre-amplifier 532 (e.g. preamp 532) and a zero-crossing receiver or edgedetect receiver. Zero-crossing receiver or edge-detect receiver comprisedetect circuit 534. Control circuit 536 enables MUX 530 to coupletransducer 502 to preamp 532. Preamp 532 amplifies a signal output bytransducer 502 corresponding to a propagated energy wave. In anon-limiting example, the first ASIC comprises both a zero-crossingreceiver and an edge detect receiver. More multiplexing circuitry inconjunction with control circuit 536 can be incorporated on the firstASIC to select between the circuits. Similarly, multiplexing circuitrycan be used to couple and operate more than one sensor. The amplifiedsignal from preamp 532 is coupled to detection circuit 534.Zero-crossing receiver is a detection circuit that identifies apropagated energy wave by sensing a transition of the signal. Arequirement of detection can be that the signal has certain transitionand magnitude characteristics. The edge-detect receiver detects apropagated energy wave by identifying a wave front of the propagatedenergy wave. The zero-crossing receiver or edge-detect receiver outputsa pulse in response to the detection of a propagated energy wave.

Positive closed loop feedback is applied upon detection of an energywave after the startup sequence. Control circuit 536 decouplesoscillator 520 from driver 524 through switch 522 and MUX 528. Controlcircuit 536 operatively enables switch 558 and MUX 528 to coupledetection circuit 534 to driver 524. A pulse generated by detectioncircuit 534 initiates the emission of a new energy wave intocompressible propagation structure 504. The pulse from detection circuit534 is provided to driver 524. The positive closed loop feedback of thecircuitry maintains the emission, propagation, and detection of energywaves in propagation structure 504.

The first ASIC further comprises a loop counter 538, time counter 540,register 542, and ADC 556. Loop counter 538, time counter 540, andregister 542 are operatively coupled to control circuit 536 to generatea precise measurement of the transit time, frequency, or phase ofpropagated energy waves during a measurement sequence. In oneembodiment, a measurement comprises a predetermined number of energywaves propagating through the compressible propagation structure 504.The predetermined number is set in the loop counter 538. The loopcounter 538 is decremented by each pulse output by detection circuit 534that corresponds to a detected propagated energy wave. The positiveclosed loop feedback is broken when counter 538 decrements to zerothereby stopping the measurement. Time counter 540 measures a totalpropagation time of the predetermined number of propagated energy wavesset in loop counter 538. The measured total propagation time divided bythe predetermined number of propagated energy waves is a measuredtransit time of an energy wave. The measured transit time can beprecisely converted to a length of compressible propagation structure504 under a stable condition of the applied parameter on the sensingassemblage. The applied parameter value can be calculated by knownrelationship between the length of compressible propagation structure504 and the parameter. A result of the measurement is stored in register542 when loop counter 538 decrements to zero. More than one measurementcan be performed and stored. In one embodiment, the precision can beincreased by raising the number of propagated energy waves beingmeasured in loop counter 538.

In the example, energy waves are propagated from transducer 506 totransducer 5. Alternatively, control circuit 536 can direct thepropagation of energy waves from transducer 502 to transducer 506whereby transducer 502 emits energy waves and transducer 506 detectspropagated energy waves. An analog to digital converter (ADC) 556 isshown coupled to an accelerometer 554. ADC 556 is a circuit on the firstASIC. It can be used to digitize an output from a circuit such asaccelerometer 554. Accelerometer 554 can be used to detect and measurewhen sensing module 200 is in motion. Data from accelerometer 554 can beused to correct the measured result to account for module 200acceleration. ADC 556 can also be used to provide measurement data fromother sensor types by providing a digitized output corresponding tovoltage or current magnitude.

A second ASIC can comprise CRC circuit 546, telemetry transmitter 548,and matching network 508. The CRC circuit 546 applies error codedetection on the packet data such as data stored in register 542. Thecyclic redundancy check computes a checksum for a data stream or packetof any length. The checksums are used to detect interference oraccidental alteration of data during transmission. Transmitter 548 iscoupled to CRC 546 and sends the data wirelessly. Matching network 550couples telemetry transmitter 512 to antenna 552 to provide an impedancematch to efficiently transfer the signal to the antenna 552. Asdisclosed above, the integration of the telemetry transmitter and sensormodules enables construction of a wide range of sizes of the sensingmodule 200. This facilitates capturing data, measuring parameters ofinterest and digitizing that data, and subsequently communicating thatdata to external equipment with minimal disturbance to the operation ofthe body, instrument, appliance, vehicle, equipment, or physical systemfor a wide range of applications. Moreover, the level of accuracy andresolution achieved by the total integration of communicationcomponents, transducers, waveguides, and oscillators to control theoperating frequency of the ultrasound transducers enables the compact,self-contained measurement module construction. In a further embodiment,the circuitry on the first and second ASICs can be combined on a singleASIC to further reduce form factor, power, and cost.

FIG. 8 is an exemplary assemblage 800 that illustrates propagation ofultrasound waves 810 within the waveguide 806 in the bi-directional modeof operation of this assemblage. In this mode, the selection of theroles of the two individual ultrasound resonators (802, 804) ortransducers affixed to interfacing material 820 and 822, if required,are periodically reversed. In the bi-directional mode the transit timeof ultrasound waves propagating in either direction within the waveguide806 can be measured. This can enable adjustment for Doppler effects inapplications where the sensing module 808 is operating while in motion816. Furthermore, this mode of operation helps assure accuratemeasurement of the applied load, force, pressure, or displacement bycapturing data for computing adjustments to offset this external motion816. An advantage is provided in situations wherein the body,instrument, appliance, vehicle, equipment, or other physical system 814,is itself operating or moving during sensing of load, pressure, ordisplacement. Similarly, the capability can also correct in situationwhere the body, instrument, appliance, vehicle, equipment, or otherphysical system, is causing the portion 812 of the body, instrument,appliance, vehicle, equipment, or other physical system being measuredto be in motion 816 during sensing of load, force, pressure, ordisplacement. Other adjustments to the measurement for physical changesto system 814 are contemplated and can be compensated for in a similarfashion. For example, temperature of system 814 can be measured and alookup table or equation having a relationship of temperature versustransit time can be used to normalize measurements. Differentialmeasurement techniques can also be used to cancel many types of commonfactors as is known in the art.

The use of waveguide 806 enables the construction of low cost sensingmodules and devices over a wide range of sizes, including highly compactsensing modules, disposable modules for bio-medical applications, anddevices, using standard components and manufacturing processes. Theflexibility to construct sensing modules and devices with very highlevels of measurement accuracy, repeatability, and resolution that canscale over a wide range of sizes enables sensing modules and devices tothe tailored to fit and collect data on the physical parameter orparameters of interest for a wide range of medical and non-medicalapplications.

Referring back to FIG. 2, although not explicitly illustrated, it shouldbe noted that the load insert sensing device 100 and associated internalcomponents move in accordance with motion of the femur 108 as shown. Thebi-directional operating mode of the waveguide mitigates the Dopplereffects resulting from the motion. As previously indicated,incorporating data from the accelerometer 121 with data from the othercomponents of the sensing module 200 helps assure accurate measurementof the applied load, force, pressure, displacement, density, localizedtemperature, or viscosity by enabling computation of adjustments tooffset this external motion.

For example, sensing modules or devices may be placed on or within, orattached or affixed to or within, a wide range of physical systemsincluding, but not limited to instruments, appliances, vehicles,equipments, or other physical systems as well as animal and humanbodies, for sensing the parameter or parameters of interest in real timewithout disturbing the operation of the body, instrument, appliance,vehicle, equipment, or physical system.

In addition to non-medical applications, examples of a wide range ofpotential medical applications may include, but are not limited to,implantable devices, modules within implantable devices, modules ordevices within intra-operative implants or trial inserts, modules withininserted or ingested devices, modules within wearable devices, moduleswithin handheld devices, modules within instruments, appliances,equipment, or accessories of all of these, or disposables withinimplants, trial inserts, inserted or ingested devices, wearable devices,handheld devices, instruments, appliances, equipment, or accessories tothese devices, instruments, appliances, or equipment. Many physiologicalparameters within animal or human bodies may be measured including, butnot limited to, loading within individual joints, bone density,movement, various parameters of interstitial fluids including, but notlimited to, viscosity, pressure, and localized temperature withapplications throughout the vascular, lymph, respiratory, and digestivesystems, as well as within or affecting muscles, bones, joints, and softtissue areas. For example, orthopedic applications may include, but arenot limited to, load bearing prosthetic components, or provisional ortrial prosthetic components for, but not limited to, surgical proceduresfor knees, hips, shoulders, elbows, wrists, ankles, and spines; anyother orthopedic or musculoskeletal implant, or any combination ofthese.

FIG. 9 is an exemplary cross-sectional view of a sensor element 900 toillustrate changes in the propagation of ultrasound waves 914 withchanges in the length of a waveguide 906. In general, the measurement ofa parameter is achieved by relating displacement to the parameter. Inone embodiment, the displacement required over the entire measurementrange is measured in microns. For example, an external force 908compresses waveguide 906 thereby changing the length of waveguide 906.Sensing circuitry (not shown) measures propagation characteristics ofultrasonic signals in the waveguide 906 to determine the change in thelength of the waveguide 906. These changes in length change in directproportion to the parameters of interest thus enabling the conversion ofchanges in the parameter or parameters of interest into electricalsignals.

As previously discussed, external forces applied to the sensing module200 compress the waveguide(s) thereby changing the length of thewaveguide(s). The sensing module 200 measures propagationcharacteristics of ultrasonic signals in the waveguide(s) to determinethe change in the length of the waveguide(s). These changes in lengthchange in direct proportion to the parameters of interest thus enablingthe conversion of changes in the parameter or parameters of interestinto load (or force) information.

As illustrated, external force 908 compresses waveguide 906 and pushesthe transducers 902 and 904 closer to one another by a distance 910.This changes the length of waveguide 906 by distance 912 of thewaveguide propagation path between transducers 902 and 904. Depending onthe operating mode, the sensing circuitry measures the change in lengthof the waveguide 906 by analyzing characteristics of the propagation ofultrasound waves within the waveguide.

One interpretation of FIG. 9 illustrates waves emitting from transducer902 at one end of waveguide 906 and propagating to transducer 904 at theother end of the waveguide 906. The interpretation includes the effectof movement of waveguide 906 and thus the velocity of waves propagatingwithin waveguide 906 (without changing shape or width of individualwaves) and therefore the transit time between transducers 902 and 904 ateach end of the waveguide. The interpretation further includes theopposite effect on waves propagating in the opposite direction and isevaluated to estimate the velocity of the waveguide and remove it byaveraging the transit time of waves propagating in both directions.

Changes in the parameter or parameters of interest are measured bymeasuring changes in the transit time of energy pulses or waves withinthe propagating medium. Closed loop measurement of changes in theparameter or parameters of interest is achieved by modulating therepetition rate of energy pulses or the frequency of energy waves as afunction of the propagation characteristics of the elastic energypropagating structure.

In a continuous wave mode of operation, a phase detector (not shown)evaluates the frequency and changes in the frequency of resonantultrasonic waves in the waveguide 906. As will be described below,positive feedback closed-loop circuit operation in continuous wave (CW)mode adjusts the frequency of ultrasonic waves 914 in the waveguide 906to maintain a same number or integer number of periods of ultrasonicwaves in the waveguide 906. The CW operation persists as long as therate of change of the length of the waveguide is not so rapid thatchanges of more than a quarter wavelength occur before the frequency ofthe propagation tuned oscillator (PTO) can respond. This restrictionexemplifies one advantageous difference between the performance of a PTOand a Phase Locked Loop (PLL). Assuming the transducers are producingultrasonic waves, for example, at 2.4 MHz, the wavelength in air,assuming a velocity of 343 microns per microsecond, is about 143μ,although the wavelength within a waveguide may be longer than inunrestricted air.

In a pulse mode of operation, the phase detector measures a time offlight (TOF) between when an ultrasonic pulse is transmitted bytransducer 902 and received at transducer 904. The time of flightdetermines the length of the waveguide propagating path, and accordinglyreveals the change in length of the waveguide 906. In anotherarrangement, differential time of flight measurements (or phasedifferences) can be used to determine the change in length of thewaveguide 906. A pulse consists of a pulse of one or more waves. Thewaves may have equal amplitude and frequency (square wave pulse) or theymay have different amplitudes, for example, decaying amplitude(trapezoidal pulse) or some other complex waveform. The PTO is holdingthe phase of the leading edge of the pulses propagating through thewaveguide constant. In pulse mode operation the PTO detects the leadingedge of with an edge-detect receiver rather than a zero-crossing ortransition as detected by a zero-crossing receiver used in CW mode.

It should be noted that ultrasound energy pulses or waves, the emissionof ultrasound pulses or waves by ultrasound resonators or transducers,transmitted through ultrasound waveguides, and detected by ultrasoundresonators or transducers are used merely as examples of energy pulses,waves, and propagation structures and media. Other embodiments hereincontemplated can utilize other wave forms, such as, light.

FIG. 10 is an exemplary block diagram 1000 of a propagation tunedoscillator (PTO) 4 to maintain positive closed-loop feedback inaccordance with an exemplary embodiment. The measurement system includesa sensing assemblage 1 and propagation tuned oscillator (PTO) 4 thatdetects energy waves 2 in one or more waveguides 3 of the sensingassemblage 1. In one embodiment, energy waves 2 are ultrasound waves. Apulse 11 is generated in response to the detection of energy waves 2 toinitiate a propagation of a new energy wave in waveguide 3. It should benoted that ultrasound energy pulses or waves, the emission of ultrasoundpulses or waves by ultrasound resonators or transducers, transmittedthrough ultrasound waveguides, and detected by ultrasound resonators ortransducers are used merely as examples of energy pulses, waves, andpropagation structures and media. Other embodiments herein contemplatedcan utilize other wave forms, such as, light.

Recall that the sensing insert device 100 when in motion measures forceson the sensing assemblies by evaluating propagation times of energywaves within the waveguides in conjunction with the accelerometer data.The propagation tuned oscillator (PTO) 4 measures a transit time ofultrasound waves 2 within the waveguide 3 in a closed-loopconfiguration. The digital counter 20 determines the physical change inthe length of the waveguide. Referring to FIG. 5, the one or moreaccelerometers 302 determines the changes along x, y and z dimensions.The electronic circuitry 307 in view of the accelerometer data fromaccelerometer 302 and the physical changes in length of the sensingassemblage 1 determines the applied loading (or forces).

The sensing assemblage 1 comprises transducer 5, transducer 6, and awaveguide 3 (or energy propagating structure). In a non-limitingexample, sensing assemblage 1 is affixed to load bearing or contactingsurfaces 8. External forces applied to the contacting surfaces 8compress the waveguide 3 and change the length of the waveguide 3. Undercompression, transducers 5 and 6 will also be moved closer together. Thechange in distance affects the transit time 7 of energy waves 2transmitted and received between transducers 5 and 6. The propagationtuned oscillator 4 in response to these physical changes will detecteach energy wave sooner (e.g. shorter transit time) and initiate thepropagation of new energy waves associated with the shorter transittime. As will be explained below, this is accomplished by way of PTO 4in conjunction with the pulse generator 10, the mode control 12, and thephase detector 14.

Notably, changes in the waveguide 3 (energy propagating structure orstructures) alter the propagation properties of the medium ofpropagation (e.g. transit time 7). The energy wave can be a continuouswave or a pulsed energy wave. A pulsed energy wave approach reducespower dissipation allowing for a temporary power source such as abattery or capacitor to power the system during the course of operation.In at least one exemplary embodiment, a continuous wave energy wave or apulsed energy wave is provided by transducer 5 to a first surface ofwaveguide 3. Transducer 5 generates energy waves 2 that are coupled intowaveguide 3. In a non-limiting example, transducer 5 is a piezo-electricdevice capable of transmitting and receiving acoustic signals in theultrasonic frequency range.

Transducer 6 is coupled to a second surface of waveguide 3 to receivethe propagated pulsed signal and generates a corresponding electricalsignal. The electrical signal output by transducer 6 is coupled to phasedetector 14. In general, phase detector 14 compares the timing of aselected point on the waveform of the detected energy wave with respectto the timing of the same point on the waveform of other propagatedenergy waves. In a first embodiment, phase detector 14 can be azero-crossing receiver. In a second embodiment, phase detector 14 can bean edge-detect receiver. In the example where sensing assemblage 1 iscompressed, the detection of the propagated energy waves 2 occursearlier (due to the length/distance reduction of waveguide 3) than asignal prior to external forces being applied to contacting surfaces.Pulse generator 10 generates a new pulse in response to detection of thepropagated energy waves 2 by phase detector 14. The new pulse isprovided to transducer 5 to initiate a new energy wave sequence. Thus,each energy wave sequence is an individual event of energy wavepropagation, energy wave detection, and energy wave emission thatmaintains energy waves 2 propagating in waveguide 3.

The transit time 7 of a propagated energy wave is the time it takes anenergy wave to propagate from the first surface of waveguide 3 to thesecond surface. There is delay associated with each circuit describedabove. Typically, the total delay of the circuitry is significantly lessthan the propagation time of an energy wave through waveguide 3. Inaddition, under equilibrium conditions variations in circuit delay areminimal. Multiple pulse to pulse timings can be used to generate anaverage time period when change in external forces occur relativelyslowly in relation to the pulsed signal propagation time such as in aphysiologic or mechanical system. The digital counter 20 in conjunctionwith electronic components counts the number of propagated energy wavesto determine a corresponding change in the length of the waveguide 3.These changes in length change in direct proportion to the externalforce thus enabling the conversion of changes in parameter or parametersof interest into electrical signals.

The block diagram 1000 further includes counting and timing circuitry.More specifically, the timing, counting, and clock circuitry comprises adigital counter 20, a digital timer 22, a digital clock 24, and a dataregister 26. The digital clock 24 provides a clock signal to digitalcounter 20 and digital timer 22 during a measurement sequence. Thedigital counter 20 is coupled to the propagation tuned oscillator 4.Digital timer 22 is coupled to data register 26. Digital timer 20,digital timer, 22, digital clock 24 and data register 26 capture transittime 7 of energy waves 2 emitted by ultrasound resonator or transducer5, propagated through waveguide 3, and detected by or ultrasoundresonator or transducer 5 or 6 depending on the mode of the measurementof the physical parameters of interest applied to surfaces 8. Theoperation of the timing and counting circuitry is disclosed in moredetail hereinbelow.

The measurement data can be analyzed to achieve accurate, repeatable,high precision and high resolution measurements. This method enables thesetting of the level of precision or resolution of captured data tooptimize trade-offs between measurement resolution versus frequency,including the bandwidth of the sensing and data processing operations,thus enabling a sensing module or device to operate at its optimaloperating point without compromising resolution of the measurements.This is achieved by the accumulation of multiple cycles of excitationand transit time instead of averaging transit time of multipleindividual excitation and transit cycles. The result is accurate,repeatable, high precision and high resolution measurements ofparameters of interest in physical systems.

In at least one exemplary embodiment, propagation tuned oscillator 4 inconjunction with one or more sensing assemblages 1 are used to takemeasurements on a muscular-skeletal system. In a non-limiting example,sensing assemblage 1 is placed between a femoral prosthetic componentand tibial prosthetic component to provide measured load informationthat aids in the installation of an artificial knee joint. Sensingassemblage 1 can also be a permanent component or a muscular-skeletaljoint or artificial muscular-skeletal joint to monitor joint function.The measurements can be made in extension and in flexion. In theexample, assemblage 1 is used to measure the condyle loading todetermine if it falls within a predetermined range and location. Basedon the measurement, the surgeon can select the thickness of the insertsuch that the measured loading and incidence with the final insert inplace will fall within the predetermined range. Soft tissue tensioningcan be used by a surgeon to further optimize the force or pressure.Similarly, two assemblages 1 can be used to measure both condylessimultaneously or multiplexed. The difference in loading (e.g. balance)between condyles can be measured. Soft tissue tensioning can be used toreduce the force on the condyle having the higher measured loading toreduce the measured pressure difference between condyles.

One method of operation holds the number of energy waves propagatingthrough waveguide 3 as a constant integer number. A time period of anenergy wave corresponds to energy wave periodicity. A stable time periodis one in which the time period changes very little over a number ofenergy waves. This occurs when conditions that affect sensing assemblage1 stay consistent or constant. Holding the number of energy wavespropagating through waveguide 3 to an integer number is a constraintthat forces a change in the time between pulses when the length ofwaveguide 3 changes. The resulting change in time period of each energywave corresponds to a change in aggregate energy wave time period thatis captured using digital counter 20 as a measurement of changes inexternal forces or conditions applied to contacting surfaces 8.

A further method of operation according to one embodiment is describedhereinbelow for energy waves 2 propagating from transducer 5 andreceived by transducer 6. In at least one exemplary embodiment, energywaves 2 is an ultrasonic energy wave. Transducers 5 and 6 arepiezo-electric resonator transducers. Although not described, wavepropagation can occur in the opposite direction being initiated bytransducer 6 and received by transducer 5. Furthermore, detectingultrasound resonator transducer 6 can be a separate ultrasound resonatoras shown or transducer 5 can be used solely depending on the selectedmode of propagation (e.g. reflective sensing). Changes in externalforces or conditions applied to contacting surfaces 8 affect thepropagation characteristics of waveguide 3 and alter transit time 7. Asmentioned previously, propagation tuned oscillator 4 holds constant aninteger number of energy waves 2 propagating through waveguide 3 (e.g.an integer number of pulsed energy wave time periods) therebycontrolling the repetition rate. As noted above, once PTO 4 stabilizes,the digital counter 20 digitizes the repetition rate of pulsed energywaves, for example, by way of edge-detection, as will be explainedhereinbelow in more detail.

In an alternate embodiment, the repetition rate of pulsed energy waves 2emitted by transducer 5 can be controlled by pulse generator 10. Theoperation remains similar where the parameter to be measured correspondsto the measurement of the transit time 7 of pulsed energy waves 2 withinwaveguide 3. It should be noted that an individual ultrasonic pulse cancomprise one or more energy waves with a damping wave shape. The energywave shape is determined by the electrical and mechanical parameters ofpulse generator 10, interface material or materials, where required, andultrasound resonator or transducer 5. The frequency of the energy waveswithin individual pulses is determined by the response of the emittingultrasound resonator 4 to excitation by an electrical pulse 11. The modeof the propagation of the pulsed energy waves 2 through waveguide 3 iscontrolled by mode control circuitry 12 (e.g., reflectance oruni-directional). The detecting ultrasound resonator or transducer mayeither be a separate ultrasound resonator or transducer 6 or theemitting resonator or transducer 5 depending on the selected mode ofpropagation (reflectance or unidirectional).

In general, accurate measurement of physical parameters is achieved atan equilibrium point having the property that an integer number ofpulses are propagating through the energy propagating structure at anypoint in time. Measurement of changes in the “time-of-flight” or transittime of ultrasound energy waves within a waveguide of known length canbe achieved by modulating the repetition rate of the ultrasound energywaves as a function of changes in distance or velocity through themedium of propagation, or a combination of changes in distance andvelocity, caused by changes in the parameter or parameters of interest.

It should be noted that ultrasound energy pulses or waves, the emissionof ultrasound pulses or waves by ultrasound resonators or transducers,transmitted through ultrasound waveguides, and detected by ultrasoundresonators or transducers are used merely as examples of energy pulses,waves, and propagation structures and media. Other embodiments hereincontemplated can utilize other wave forms, such as, light. Furthermore,the velocity of ultrasound waves within a medium may be higher than inair. With the present dimensions of the initial embodiment of apropagation tuned oscillator the waveguide is approximately threewavelengths long at the frequency of operation.

Measurement by propagation tuned oscillator 4 and sensing assemblage 1enables high sensitivity and high signal-to-noise ratio. The time-basedmeasurements are largely insensitive to most sources of error that mayinfluence voltage or current driven sensing methods and devices. Theresulting changes in the transit time of operation correspond tofrequency, which can be measured rapidly, and with high resolution. Thisachieves the required measurement accuracy and precision thus capturingchanges in the physical parameters of interest and enabling analysis oftheir dynamic and static behavior.

These measurements may be implemented with an integrated wirelesssensing module or device having an encapsulating structure that supportssensors and load bearing or contacting surfaces and an electronicassemblage that integrates a power supply, sensing elements, energytransducer or transducers and elastic energy propagating structure orstructures, biasing spring or springs or other form of elastic members,an accelerometer, antennas and electronic circuitry that processesmeasurement data as well as controls all operations of ultrasoundgeneration, propagation, and detection and wireless communications. Theelectronics assemblage also supports testability and calibrationfeatures that assure the quality, accuracy, and reliability of thecompleted wireless sensing module or device.

In general, measurement of the changes in the physical length ofindividual waveguides can be made in several modes. Each assemblage ofone or two ultrasound resonators or transducers combined with awaveguide can be controlled to operate in six different modes. Thisincludes two wave shape modes: continuous wave or pulsed waves, andthree propagation modes: reflectance, unidirectional, and bi-directionalpropagation of the ultrasound wave. In all modes of operation thechanges in transit time within the ultrasound waveguides change theoperating frequency of the propagation tuned oscillator 4 oroscillators. These changes in the frequency of oscillation of thepropagation tuned oscillator or oscillators can be measured rapidly andwith high resolution. This achieves the required measurement accuracyand precision thus enabling the capture of changes in the physicalparameters of interest and enabling analysis of the dynamic and staticbehavior of the physical system or body.

The level of accuracy and resolution achieved by the integration ofenergy transducers and an energy propagating structure or structurescoupled with the electronic components of the propagation tunedoscillator enables the construction of, but is not limited to, compactultra low power modules or devices for monitoring or measuring theparameters of interest. The flexibility to construct sensing modules ordevices over a wide range of sizes enables sensing modules to betailored to fit a wide range of applications such that the sensingmodule or device may be engaged with, or placed, attached, or affixedto, on, or within a body, instrument, appliance, vehicle, equipment, orother physical system and monitor or collect data on physical parametersof interest without disturbing the operation of the body, instrument,appliance, vehicle, equipment, or physical system.

FIG. 11 is a cross-sectional view of a layout architecture of thesensing module 200 in accordance with an exemplary embodiment. Theblocks are operatively coupled within the encapsulated enclosure of thesensing module 200 and together form an encapsulated force sensor 1100.It comprises a top steel plate 1104 coupled to a lower printed circuitboard (PCB) 1118 by way of spring retainer 1106, disc spring 1108, andspring post 1114. The force sensor 1100 is biased with springs, anelastic support structure or other means to accurately maintain arequired distance between the load bearing or contact surfaces such astop cover 1102 and to minimize hysteresis due to material properties ofwaveguide 1110.

The encapsulating force sensor 1100 supports and protects thespecialized mechanical and electronic components from external physical,mechanical, chemical, and electrical, and electromagnetic intrusion thatmight compromise sensing or communication operations of the module ordevice. The encapsulating force sensor 1100 also supports internalmechanical and electronic components and minimizes adverse physical,mechanical, electrical, and ultrasonic interactions that mightcompromise sensing or communication operations of the module or device.Top cover 1102 and unitary main body 1157 form the encapsulatingenclosure. Unitary main body 1157 is a metal, plastic, or polymer bodyhaving sufficient strength and rigidity to withstand forces, pressures,and loads of the muscular-skeletal system. In particular, the sidewallsor bottom surface do not deform under normal operating conditions. Forexample, the unitary main body 1157 can be formed of polycarbonate orother biocompatible material. Moreover, unitary main body 1157 can bemolded in a manufacturing process that allows detailed features to berepeatably and reliably manufactured.

The physical layout architecture of sensor 1100 has the one or moresensing assemblages overlying the electronic circuitry. A force,pressure, or load is applied to a surface of sensor 1100. The surface ofsensor 1100 corresponds to top steel plate 1104. Steel plate 1104 movesin response to a force, pressure, or load. The steel plate 1104 cansupport the movement while maintaining a seal with unitary main body1157 that isolates an interior of the enclosure. In general, a sensingassemblage is coupled between steel plate 1104 and a substrate 1130.Substrate 1130 is a rigid non-moveable substrate that is supported bythe sidewalls of unitary main body 1157. A periphery of substrate 1130is in contact with and supported by a support feature 1128 formed in thesidewalls of unitary main body 1157. Substrate 1130 does not flex underloading. The sensing assemblage translates a displacement due to theforce, pressure, or load applied to steel plate 1104 to a signal. Thesignal is processed by electronic circuitry in the enclosure to generatedata corresponding to the force, pressure, or load value. As shown, thesensing assemblage comprises upper piezo 1112, waveguide 1110, and lowerpiezo 1124. Upper piezo 1112 and lower piezo 1124 are ultrasonicpiezo-electric transducers.

Electronic circuitry to power, control, interface, operate, measure, andsend sensor data is interconnected together on a printed circuit board(PCB) 1118. One or more cups 1120 are formed in unitary main body 1157.In one embodiment, the components mounted on PCB 1118 reside within cups1120. One or more structures 1126 support and fix the position of thePCB 1118. The components on PCB 1118 are suspended in the cups 1120 anddo not have contact with unitary main body 1157 thereby preventinginterconnect stress that could result in long-term reliability issues.The PCB 1118 is mechanically isolated from substrate 1130. Thus, anyforce, pressure, or loading on substrate 1130 is not applied to PCB1118. Flexible interconnect is used to connect from the electroniccircuitry on PCB 1118 to upper piezo 1112 and lower piezo 1124.

In one embodiment, more than one sensing assemblage couples topredetermined locations of the steel plate 1104. Each sensing assemblagecan measure a parameter applied to steel plate 1104. In combination, thesensing assemblages can determine a location or region where theparameter is applied to the surface. For example, the magnitude andposition of the loading on the contacting surface of sensing module 200applied by femur 102 and tibia 108 to sensing module 200 can be measuredand displayed as shown in FIG. 2. In a non-limiting example, threesensing assemblages can be spaced on a periphery of steel plate 1104. Inthe example, each sensing assemblage will measure a force applied tosteel plate 1104. The location of the applied force is closest to thesensing assemblage detecting the highest force magnitude. Conversely,the sensing assemblage detecting the weakest force magnitude is farthestfrom the applied force. The measured force magnitudes in combinationwith the predetermined locations where the sensing assemblages couple tosteel plate 1104 can be used to determine a location where the parameteris applied.

The housing electrically insulates the internal electronic, sensing, andcommunication components. The encapsulating force sensor 1100 eliminatesparasitic paths that might conduct ultrasonic energy and compromiseexcitation and detection of ultrasound waves within the sensingassemblages during sensing operations. A temporary bi-directionalelectrical interconnect assures a high level of electrical observationand controllability of the electronic assembly within the encapsulatingforce sensor 1100. The temporary interconnect also provides a high levelof electrical observation of the sensing subsystem, including thetransducers, waveguides, and mechanical spring or elastic assembly.

Ultrasound waveguide 1110 is coupled to the top cover 1102. A forceapplied to the top cover 1102 compresses waveguide 1110. Lower piezo1124 and upper piezo 1112 are piezo-electric transducers respectivelycoupled to waveguide 1110 at a first and second location. Waveguide 1110is a compressible propagation medium for ultrasonic energy waves. Thetransducers emit energy waves and detect propagated energy waves inwaveguide 1110. Electronic circuitry is coupled to lower piezo 1124 andupper piezo 1112 to measure transit time, frequency, or phase of thepropagated energy waves. The transit time, frequency, or phase of energywaves propagating between the first and second locations of waveguide1110 can be precisely measured and therefore the length of theultrasound waveguide 1110. The length of waveguide 1110 is calculated bya known function relating material properties of the waveguide 1110 tothe parameter being measured. In the example, a force, pressure, or loadis calculated from the measured length of waveguide 1110.

The encapsulated force sensor 1100 can accurately and repeatably measureone pound changes in load with changes in length of a waveguidecomprising 2.5 microns. The maximum change in the present implementationis specified at less than 5.0 microns. This assures that the size of thesensing module 200 throughout all measurements remains within therequired dimension (e.g., distance) of the insert between the loadbearing surfaces of the prosthetic components.

An exemplary level of control of the compression or displacement of thewaveguides 1110 with changes in load, force, pressure, or displacementis achieved by positioning the spring or springs 1108, elastic supportstructure, or other means of elastic support, including the waveguides1110 themselves, between the load bearing contact surfaces to minimizeany tendency of the load bearing contact surfaces to cantilever.Cantilevering can compromise the accuracy of the inclination of the loadbearing contact surface whenever load, force, pressure, or displacementis applied to any point near a periphery of the load bearing contactsurfaces. In one embodiment, springs 1108 are disc springs. The spring1108 is held in a predetermined location by spring post 1114 and springretainer 1104.

The walls of the unitary main body 1157 include a small gap to enablethe steel plate 1104 to move. The hermetic seal is also flexible toallow the steel plate 1104 of the force sensor 1104 to slide up anddown, like a piston, for distances on the order of a hundred micronswithout compromising integrity of the seal. The hermetic seal completesmanufacturing, sterilization, and packaging processes withoutcompromising ability to meet regulatory requirements for hermeticity.The level of hermeticity is sufficient to assure functionality andbiocompatibility over the lifetime of the device. Implant devices withtotal implant time less than 24 hours may have less stringent regulatoryrequirements for hermeticity. Unbiased electrical circuitry is lesssusceptible to damage from moisture. The electronics in one embodimentare only powered during actual usage. In another embodiment, theencapsulated force sensor 1100 employs low duty cycles to serve as ameasurement-on-demand device to efficiently perform at low totaloperating time when the electronics are powered on.

The encapsulating force sensor 1100 has a compact size permitting it tofit for example within a trial insert, final insert, prostheticcomponent, tool, equipment, or implant structure to measure the leveland incidence of the load on subsequent implanted prosthetic devices. Itcan be constructed using standard components and manufacturingprocesses. Manufacturing carriers or fixtures can be designed to emulatethe final encapsulating enclosure of the sensing module 200. Calibrationdata can be obtained during the manufacturing processing thus enablingcapture of accurate calibration data. These calibration parameters canbe stored within the memory circuits integrated into the electronicsassemblage of the sensing module 200. Testability and calibrationfurther assures the quality and reliability of the encapsulatedenclosure.

Examples of a wide range of potential medical applications can include,but are not limited to, implantable devices, modules within implantabledevices, intra-operative implants or modules within intra-operativeimplants or trial inserts, modules within inserted or ingested devices,modules within wearable devices, modules within handheld devices,modules within instruments, appliances, equipment, or accessories of allof these, or disposables within implants, trial inserts, inserted oringested devices, wearable devices, handheld devices, instruments,appliances, equipment, or accessories to these devices, instruments,appliances, or equipment.

FIG. 12 is a simplified cross-sectional view of an embodiment of theload sensing platform 121 in accordance with an exemplary embodiment.The load sensing platform 121 is placed, engaged, attached, or affixedto or within a physical system with a portion of the system contactingthe load bearing or contacting surfaces of the load sensing platform121. As disclosed in FIG. 1 the load sensing platform 121 can be usedintra-operatively to measure parameters of the muscular-skeletal systemduring joint replacement surgery. In the example, the load bearingplatform 121 is placed in a joint of the muscular-skeletal system tomeasure force, pressure, or load and the location where the force,pressure, or load is applied. The lower load bearing surface 8 contactsthe tibial component 106 of the artificial knee. The upper load bearingsurface 8 contacts the femoral component 104 of the artificial knee. Notshown are the muscles, ligaments, and tendons of the muscular-skeletalsystem that apply a compressive force, pressure, or load on the surfaces8 of the load sensing platform 121. The load sensing platform 121 has aform factor that allows integration in tools, equipment, and implants.The load sensing platform 121 is bio-compatible and can be placed in animplant or attached to the muscular-skeletal system to provide long termmonitoring capability of natural structures or artificial components.

A compact sensing platform is miniaturized to be placed on or within abody, instrument, appliance, vehicle, equipment, or other physicalsystem without disturbing the operation of the body, instrument,appliance, vehicle, equipment, or physical system. This facilitatescontacting the sources of load, force, pressure, displacement, density,viscosity, or localized temperature to be measured. The non-limitingexample of load sensing platform 121 can include circuitry disclosed inFIG. 5. Two or more springs or other means of elastic support 315support the load bearing or contacting surfaces 8. One or moreassemblages each comprised of one or two ultrasound resonators ortransducers are coupled between load bearing surfaces 8.

As shown, a single sensing assemblage 1 is centrally located in loadsensing platform 121. Sensing assemblage 1 is a stack comprising theupper transducer 6, the lower transducer 5, and the waveguide 3. In oneembodiment, the waveguide 3 is cylindrical in shape having a first endand a second end. Transducers 5 and 6 respectively overlie the first andsecond ends of waveguide 3. An interface material can be used to attachand enhance acoustical coupling between a transducer and waveguide. Thestack is positioned in contact with, attached, or coupled to the loadbearing or contacting surfaces 8. Electrical interconnect such as a flexinterconnect couples to terminals of transducers 5 and 6. The flexinterconnect (not shown) electrically connects transducers 5 and 6 toelectronic circuitry 307 of the sensing module 200.

The upper load bearing surface 8 is a surface of an upper substrate 702.An interior surface of the upper substrate 702 couples to transducer 6.Similarly, the lower load bearing surface 8 is a surface of a lowersubstrate 704. An interior surface of the lower substrate couples to thetransducer 5. A load, force, or pressure applied across load bearingsurfaces 8 can compress or lengthen waveguide 3. This arrangementfacilitates translating changes in the parameter or parameters ofinterest into changes in the length or compression of the waveguide orwaveguides 3 and converting these changes in the length or compressionof the waveguide 3 or waveguides into electrical signals by way oftransducers 5 or 6 thus enabling sensing assemblage 1 to sense changesin the physical parameters of interest with minimal disturbance to theoperation of the external body, instrument, appliance, vehicle,equipment, or physical system. To achieve the required level ofminiaturization, the length of the ultrasound waveguides 3 is on theorder of 10 millimeters in length. The measurable resolution ofcompression or displacement of waveguide is on the order of sub-microns.

One or more springs 315 or other means of elastic support, support theload bearing or contacting surfaces 8. The one or more springs control acompression of load sensing platform 121. For example, waveguide 3 cancomprise a polymer material suitable for energy wave propagation. In oneembodiment, the polymer material changes dimension when a parameter tobe measured is applied to waveguide 3. A relationship is known betweenthe polymer material and a measured dimension. Changes in dimension aremeasured and the parameter calculated by way of the known relationship.The polymer material can exhibit mechanical hysteresis whereby thematerial in-elastically responds to changes in the applied parameter. Inthe example, the length of waveguide 3 responds to the force, pressure,or load applied across contacting surfaces 8. Moreover, the polymermaterial may not rebound in a timely fashion as the force, pressure orload changes. Springs 315 aid in the transition as waveguide 3 respondsto different levels of compression. Springs 315 bring the load sensingplatform 121 to an accurate and repeatable quiescent state or condition.Springs further prevent the cantilevering of load bearing surfaces 8that can reduce an accuracy of measurement. Cantilevering becomes moreprevalent as forces, pressures, and loads are applied towards theperiphery of a contact area of load bearing surfaces 8.

In one embodiment, the springs 315 that support load bearing surfaces 8are disc springs or a wave springs. Disc springs are capable ofmaintaining waveguide 3 at a precise length. The compression of thewaveguide 3 is very accurate over the measurement range. The compressionof the disc springs can be monotonic over the range of applied levels offorce, pressure, or load. In one embodiment, the surfaces of the discsprings are polished to assure smooth compression with changes in forceapplied to contact surfaces 8. A further benefit of the disk springs isthat they eliminate or minimize cantilevering of the load supportingsubstrate that can compromise the accuracy due to the inclination ofload bearing surfaces 8. In the illustration, two springs 315 are shownthat are located on the periphery of load sensing platform 121. Althoughnot shown, other springs 315 may reside in the load sensing platform 121at other predetermined locations. Typically, the contact area where theparameter is applied to load bearing surfaces 8 is within an areabounded by springs 315.

In one embodiment, a substrate 706 is resides between upper substrate702 and lower substrate 704. Sensing assemblage 1 couples through anopening in substrate 706 to couple to the interior surfaces ofsubstrates 702 and 704 to measure a force, pressure, or load appliedacross load bearing surfaces 8. In the example, substrate 702 moves as aforce, pressure, or load is applied while substrate 704 remains in afixed position. Thus, a force, pressure, or load applied to contactingsurface 8 changes a distance between substrates 702 and 704 andtherefore the length of waveguide 3. Substrates 704 and 706 are planarto one another separated by a predetermined spacing. Substrates 704 and706 remain in the fixed relation to one another under loading.

Springs 315 are placed between an upper surface of substrate 706 and theinterior surface of substrate 702. As disclosed in the example, springs315 are disc springs. The disc springs are concave in shape. The discspring is formed having a centrally located circular opening. Thesurface of springs 315 proximally located to the circular openingcontacts the upper surface of substrate 706. The surface of springs 315proximally located to the outer edge of springs 315 contacts theinterior surface of substrate 702. A force applied across the loadbearing surface 8 of load sensing platform 121 will compress springs 315and waveguide 3. The amount of compression of waveguide 3 over ameasurable range can be very small but will provide precision accuracyof the parameter. For example, waveguide 3 may be compressed less than amillimeter for a force measurement ranging from 5 to 100 lbs. In theexample, the length of waveguide 3 is precisely measured using acousticenergy wave propagation. The measured length is then converted to theforce, pressure, or load. The springs 315 support movement of thewaveguide 3 upon a change in force, pressure, or loading. For example,springs 315 repeatably return the load sensing platform 121 to a precisequiescent state upon releasing an applied force. The characteristics ofsprings 315 are known over the measurement range of load sensingplatform 121. The calculated measured value of the parameter can includecompensation due to springs 315.

Spring 315 are in a fixed location in load sensing platform 121. Thedisc springs are located on the periphery of the load sensing platform121. Spring posts 708 and spring retainers 710 are used to align and fixsprings 315 in each predetermined location. Spring post 708 alignssubstrate 702 to substrate 706. Spring post 708 and spring retainer 710aligns to corresponding openings in substrate 706. In one embodiment, acap of post 708 fits into a corresponding cavity of the interior surfaceof substrate 702. Spring retainer 710 is a sleeve that overlies post708. Post 708 and spring retainer 710 couples through a correspondingopening in substrate 706. Spring retainer 710 has a lip that overliesand contacts the upper surface of substrate 706. The spring post 708 andspring retainer 710 couple through the opening in the disc spring. Theedge of the opening rests against the edge of the lip of retainer 710thereby retaining and holding spring 315 in the predetermined location.Spring 315 can move vertically allowing waveguide 3 to change length dueto the parameter being applied to contact surfaces 8.

In one embodiment, load sensing platform 121 can locate a position wherethe parameter is applied on a load bearing surface. Locating theposition can be achieved by using more than one sensing assemblages 1.In one embodiment, three sensing assemblages 1 couple to load bearing orcontacting surface 8 at three predetermined locations. The parameter ismeasured by each sensing assemblages 1. The magnitudes of eachmeasurement and the differences between measurements of the sensingassemblages 1 are compared. For example, the location of the appliedparameter is closer to the sensing assemblage that generates the highestreading. Conversely, the location of the applied parameter will befurthest from the sensing assemblage that generates the lowest reading.The exact location can be determined by comparison of the measuredvalues of each sensing assemblage in conjunction with knowledge of thepredetermined locations where each assemblage contacts load bearing orcontacting surface 8.

FIG. 14 is an exemplary block diagram schematic of a compact low-powerenergy source 1400 integrated into an exemplary electronic assembly ofthe sensing module 200 in accordance with one embodiment. The schematicillustrates one embodiment of the capacitive energy storage 1400 havingan induction coupling to an external power source 1402 to transferenergy to a super capacitor or capacitor as an energy storage devicethat provides operating power for sensing module 200. The compactlow-power energy source 1400 can comprise an induction coil 1404, arectifier 1406, a regulator 1408, a capacitive energy storage device1410, a power management circuit 1412, and operational circuitry 1414.The latter circuits can be analog or discrete components, assembled inpart or whole with other electronic circuitry, custom designed as anASIC, or any combination thereof. In one embodiment, the operationalcircuitry can include circuitry to operate and produce measurement datafrom sensing assemblages, demodulation circuitry for a wireless receivepath, communication circuitry, and secure encoding circuitry.

The external energy source 1402 can be coupled to a battery or batteriesor an alternating current power supply. For example, external energysource 1402 can be an external hand-held device with its own batterythat wirelessly transfers charge from the battery of the hand-helddevice to the energy source 1400 of the sensing device. The surgeon ortechnician can hold the hand-held device in close proximity to thesensing device prior to or during orthopedic surgery to providesufficient charge to operate the device during the procedure. Thesensing device as a long-term implant can be charged by the patient athis or her own convenience to initiate a measurement process thatprovides information on the implant status. In other embodiments, thesensing module 200 being powered by charge from external energy source1402 can communicate a signal to indicate a recharging operation isnecessary, for example, when in the proximity of a charging device.

External energy source 1402 can be coupled wirelessly to capacitiveenergy storage device 1410 through electromagnetic induction coil orcoils 1404, rectifier 1406 and regulator 1408. The charging operation iscontrolled by power management circuitry 1412. During operation ofoperating circuitry 1414, power is transferred from capacitive energystorage device 1410 by power management circuitry 1412 that includes,but is not limited to, efficient step-up and step-down voltage convertercircuitry that conserves operating power of circuit blocks at theminimum voltage levels that support the required level of performance.Clock frequencies are also optimized for performance, power, and size toassure digital circuit blocks operate at the optimum clock rates thatsupport the required level of performance. Circuit components arepartitioned among integrated circuits and discrete components tominimize power consumption without compromising performance.Partitioning functions between digital and analog circuit also enhancesdesign flexibility and facilitates minimizing power consumption withoutsacrificing functionality or performance.

A method of powering and operation of the sensing module is disclosedbelow. The method can be practiced with more or less than the number ofsteps shown and is not limited to the order shown. To describe themethod, reference will be made to the components of other figuresdescribed hereinabove although it is understood that the method can beimplemented in any other manner using other suitable components. Thesensing module 200 described in FIG. 5 including capacitive energystorage capability and highly efficient, low power operating performancecan be used to illustrate the operating principles of the method. Themethod is initiated when the external power source 1402 beginstransmitting power within range of the induction coil or coils 1404 ofthe sensing module 200. In a second step, the induction coils 1404 arecoupled to the electromagnetic waves such that the electromagnetic wavesare sensed. The induction coil or coils 1404 are energized by the powertransmissions from external power source 1402. In a third step, thecoupled electromagnetic waves create an AC power signal in inductioncoil or coils 1404. In a fourth step, the rectifier 1406 rectifies theAC power signal to produce a rectified power signal. In one embodiment,a voltage level across induction coil or coils 1404 rises to a levelthat a rectified signal is generated by full-wave rectifier 1406. In afifth step, the rectified power signal is used to charge or provideenergy to the capacitive energy storage device 1410, which holds thecharge. In a non-limiting example, the energy storage device 1410 is asuper capacitor or capacitor having a small form factor with enoughstorage capability to power the sensing module 200 for a predeterminedperiod of time. For example, a total knee reconstruction operation takesapproximately one to two hours. Capacitive energy storage device 1410would store sufficient charge to power the sensing module 200 to providemeasurements for this length of time. Integrating most of the circuitryon one or two low-power ASICs greatly reduces power consumption of thesystem making this possible. In a sixth step, the voltage regulator 1408ensures that the capacitive energy storage device 1410 is charged to,and maintains a voltage level that is greater than the requiredoperating voltage of the sensing module 200. In a seventh step, thepower management circuitry 1412 monitors the level of charge oncapacitive energy storage device 1410 to determine if the voltageexceeds a threshold. The threshold can correspond to a shunt thresholdestablished by the regulator 1408. The operating electronics circuitry1414 is enabled when it is determined in that an adequate level ofcharge has been stored to power the sensing module 200 for at least thepredetermined time period.

In an eighth step, the power management circuitry 1412 disconnects theenergy storage device 1410 from the charging circuitry (1404, 1406, and1408) when the coupling with external power source 1402 is removed orterminated. Power management circuitry 1412 continues to monitor thelevel of charge on capacitive energy storage device 1410. The powermanagement circuitry 1412 powers down the sensing module 200 includingthe operational circuitry 1414 when the charge or voltage level fallsbelow a predetermined threshold. The power management circuitry 1412subsequently discharges remaining charge on the energy storage device1410 to prevent unreliable, intermittent, or erratic operation of theoperational circuitry 1414.

Under nominal conditions, a charge time from zero charge to fullycharged is approximately 3 minutes. In one embodiment, the maximumcharge time is specified to be no greater than 7 minutes. The chargingtime of a capacitor powered system is a major improvement over the twohours or more required to fully charge a battery from zero chargeregardless of battery capacity. The capacitive energy storage device1410 can include capacitors with solid dielectrics that have longerlifetimes than batteries, can be left uncharged, and will not degraderegardless of length of time at a zero charge. In one arrangement, thewireless charging operation can be performed by electromagneticinduction before removal of any sterile packaging. The capacitive energystorage device 1410 is applicable for powering chronic activeimplantable devices where data collection is discrete point-of-timemeasurements rather than continuous, fulltime data collection andstorage.

The compact low-power energy source can be used as a backup power sourcefor sensing module 200 should the primary power source be terminated. Amethod performed by the compact low-power energy source as a backuppower source is disclosed below. The method can be practiced with moreor less than the number of steps shown and is not limited to the ordershown. To describe the method, reference will be made to the componentsof FIGS. 1, 5 and 14, although it is understood that the method can beimplemented in any other manner using other suitable components. Themedical sensing device 100 described in FIG. 1 including capacitiveenergy storage capability and highly efficient, low power operatingperformance can be used to illustrate the operating principles of methodas a back-up power source. Broadly stated, the method is directed tocharging the sensing insert device 100 by way of a wired connectioninstead of wireless induction charging.

In a first step, the induction coil 1404 is electrically decoupled. In asecond step, the rectifier 1406 and the regulator 1408 are disabled. Atthis juncture, the method enters a state where capacitive energy storagedevice 1410 is decoupled from the wireless charging circuits; that is,the power transmission components inductor 1404, rectifier 1406, andregulator 1408 are disabled. As one example, an electrical switchingoperation disengages the connection upon the power management circuitry1412 detecting a direct line charge on the capacitive energy storagedevice 1410. In another arrangement, the power management circuitry 1412further checks whether the induction coils are energized at the time ofthe applied line charge, thereby indicating that the energy is beingdelivered via a wired connection instead, since no induction activity byan external power source 1402 is detected.

In a second step, the wired energy source starts and charges capacitiveenergy storage device 1410. The wired energy source maintains capacitiveenergy storage device 1410 at full charge under normal operatingconditions through direct electrical coupling. Power managementcircuitry 1412 monitors the level of charge on capacitive energy storagedevice 1410. If at a third step, power from wired energy source isinterrupted, power management circuitry 1412 isolates the capacitiveenergy storage device 1410 from the wired energy source. As one example,a power interruption occurs when an individual manually disconnects thewired power source from the sensing module 200. This could also occur inresponse to an energy spike or power drop in the wired energy source. Asanother example, a power interruption could occur upon the powermanagement circuitry 1412 detecting the presence of an external powersource 1402 attempting to charge the sensing module 200 and therebycompeting with the wired energy source.

In a fourth step, the power management circuitry 1412 can commence tosupply the energy stored on the capacitive energy storage device 1410 tooperating circuitry 1414 and associated electronics for normaloperation. In a fifth step, power management circuitry 1412 monitors thelevel of charge on capacitive energy storage device 1410. In a sixthstep, the power management circuitry 1412 will allow the continuedsupply of energy to the operating circuitry 1414 as long as the voltageon capacitor 1410 exceeds a voltage threshold. In a seventh step, thepower management circuitry 1412 powers down the electronic assembly whenthe charge or voltage level falls below the predetermined charge ofvoltage threshold. The threshold is chosen to provide sufficient time topower down the operational circuitry 1414 in an orderly fashion.

If the wired energy source is restored, power management circuitry 1412resumes the direct connection of power between the wired energy sourceand operational circuitry 1414. Power management circuitry 1412 alsoresumes the coupling of power between the wired energy source andcapacitive energy storage device 1410 and resumes maintaining it at fullcharge.

A method is disclosed for wireless modulation telemetry in accordancewith one embodiment. The method can be practiced with more or less thanthe number of steps shown and is not limited to the order shown. Todescribe the method, reference will be made to the components of FIGS.1, 5 and 14, although it is understood that the method can beimplemented in any other manner using other suitable components.

In a first step, the external wireless energy source 125 acquires inputdata. As one example, the user can manually enter the input data via atouchscreen or a user interface menu on the external wireless energysource 125. In another arrangement, the input data in response to a userdirective can be communicatively uploaded to the external wirelessenergy source 125, for example, by USB or via a wi-fi connection. Theinput data can be information such as a serial number, a registrationcode, biasing parameters (e.g., spring constants, load balancing),updated parameters, version control information, security codeinformation, data log tags, operational control information, or anyother data. More specifically, data and instructions to be transmittedto the sensing insert device 100 is input into a data input port 128 ofexternal wireless energy source 125.

As one example, referring back briefly to FIG. 1, the receiver station110 can query a serial number from the sensing insert device 100 forupdating medical records and inventory. Sensing insert device 100includes the sensing module 200. As another example, the externalwireless energy source 125 can download an operation code for adjustinga bias level of one of the springs in the sensing assemblies 303, orestablishing an operating mode (e.g., standby, debug, flash). Followingthe acquisition of input data, the external wireless energy source 125can be placed in the proximity of the load insert sensing device 100. Atthis point, operation of an external charging device or wireless energysource 1402 is initiated and contact is established with insert sensingdevice 100.

In a second step, the external wireless energy source 125 proceeds withsecure encoding of the input data. As one example, the external wirelessenergy source 125 by way of a processor embeds cyclic redundancy check(CRC) bits into a data communication packet representing the input data.The CRC is computed and included in the transmission of each datapacket. The cyclic redundancy check is based on an algorithm thatcomputes a checksum for a data stream or packets of any length. Thesechecksums can be used to detect interference or accidental alteration ofdata during transmission. Cyclic redundancy checks are good at detectingerrors caused by electrical or electromagnetic noise and thereforeenable robust protection against improper processing of corrupted dataencoded in energy streams having communication of instructions and dataas a secondary function.

In a third step, the external wireless energy source 125 modulates theinput data onto a TX (transmit) power signal. For instance, themodulation circuit 127 modulates the power signal as a carrier signaland conveys the input data by adjusting at least one of an amplitude,phase, or frequency of the power signal. In the case of wireless energytransfer by resonant induction, the external wireless energy source 125can modulate the resonant frequency over a small bandwidth to convey theinput data in a power efficient manner. In yet another arrangement,timing intervals between energy emissions can be used to convey inputdata. In a fourth step, the external wireless energy source 125transmits the TX power signal to the sensing insert device 100.

In a fifth step, the sensing insert device 100 senses theelectromagnetic energy waves on the induction coils. In a sixth step, aRX power signal is generated from the received electromagnetic waves.This RX power signal comprises a power signal to provide charge to powerto the sensing insert device 100 and a communication signal. Aspreviously discussed, the compact low-power energy source 1400 by way ofthe induction coils 1404, rectifier 1406, and regulator 1408 sense andconvert electromagnetic waves to a rectified voltage signal that is thenused to charge a super capacitor or capacitor. In one configuration, theexternal wireless energy source 125 and the compact low-power energysource 1400 employ resonant inductive coupling to provide powerefficient transmission over short distances (e.g., less than 20 cm). Asan example, the inductors (coils) in conjunction with closely spacedcapacitor plates are tuned to a mutual resonant frequency to minimizepower loss. The external wireless energy source 125 modulates the powersignal around the resonant frequency to transmit power efficiently whilesimultaneously conveying the communication signal.

In a seventh step, the sensing insert device 100 demodulates thecommunication signal from the RX power signal. The demodulation extractsthe information or data from the modulated carrier wave. Thedemodulation circuit can be in one of the rectifier 1406, regulator1408, power management circuitry 1412, or operational circuitry 1412. Inan eight step, the sensing insert device 100 securely decodes andvalidates the information or data. In one embodiment, a cyclicredundancy check checksum is performed to verify the data was notcorrupted or received incorrectly. The data is forwarded to control andprocessing circuitry 307. In the example, electronic circuitry 307 is onan ASIC integrated circuit with the communication blocks to perform thedemodulation, CRC, encoding/decoding, and data validation. As anexample, the circuitry can include envelope detectors, phase detectors,oscillators, multipliers, adders, filters, and logic operators.

The sensing insert device 100 can then proceed to use the decodeddown-link data, for example, to control at least one operation, as shownin a ninth step. As an example, the control operation can place thesensing insert device 100 in a particular operation mode, such as,stand-by or low-power. As another example, the control operation candownload a serial number to a local memory on the sensing insert device100. The serial number can later be transmitted upon request to acommunicatively coupled receiver station 110.

Methods are disclosed hereinbelow for power conservation in accordancewith one or more embodiments. The methods can be practiced with more orless than the number of steps shown and is not limited to the ordershown. To describe the method, reference will be made to the componentsof FIGS. 1, 5 and 14, although it is understood that the method can beimplemented in any other manner using other suitable components. Ingeneral, a sensing module 200 is coupled to the muscular-skeletalsystem. The sensing module 200 is used intra-operatively to measure oneor more parameters of the muscular-skeletal system to aid in theinstallation of prosthetic components. In the example disclosed above,the sensing module 200 is placed in a trial insert that dimensionally issubstantially equal to the dimensions of a final insert. The trialinsert is used in conjunction with other final or permanent prostheticcomponents to determine fit, function, and allowing modification to finetune the installation before the final insert is inserted. Similarly,one or more of the final prosthetic components can include sensingmodule 200. The disclosed example has the sensing module 200 in thefinal insert. The sensing modules 200 in the final prosthetic componentscan measure different parameters than the trial insert. For example,pain, infection, joint kinematics, and bearing surface wear arepost-operative parameters of interest.

In both the intra-operative and post-operative examples, the sensingmodule 200 has a form factor that is dimensionally smaller than aprosthetic component. In one embodiment, wired connections for power andcommunication are not used. In an intra-operative environment, wiredconnections can get in way of the procedure and limit surgical access.Internal implanted prosthetics such as knee, hip, spine, shoulder, andother joint implants cannot be wired unless terminals protrude throughthe skin. This is typically not desirable nor an effective long-termsolution. The sensing module 200 can incorporate a battery as atemporary power source. As disclosed above, the battery poses thelogistical problems of shelf life, installation, charging, andbiological hazard. An alternative solution to a battery is using a superor ultra capacitor to power the sensing module 200. The capacitor hasthe benefits of form factor, long life, and fast charging time in asolid-state device.

The one limitation of a capacitor is the tradeoff of form factor andcharge storage. A super or ultra capacitor having a form factor equal toor smaller than a watch battery or other small battery will typicallyhave less energy capability than the battery. In an intra-operativeprocedure, such as a total knee reconstruction, the sensing module 200has to deliver precision measurements throughout the surgery. A typicalimplant operation can last from one hour to several hours. Similarly,the sensing module 200 in a final prosthetic component would need tolast a sufficient time to run through one or more measurements of one ormore parameters. In both intra-operative and post-operativemeasurements, the measured parameter data would be sent wirelessly tothe surgeon, patient, or healthcare provider. The measured data can besent in real-time for display or delayed to be reviewed or analyzed atan appropriate time. In general, powering the sensing module 200 with acapacitor would not be a viable solution using off the shelf electroniccomponents or sensors. A capacitor meeting the form factor requirementswould not store sufficient charge to sustain device operation for arequired operational period of time.

Sensing module 200 comprises a compact low-power energy source 1400 thatincludes the capacitor 1410 that powers the device during a measurementprocess. The capacitor 1410 is able to sustain operation of sensingmodule 200 by incorporating power management circuitry 1412 having oneor more power conservation modes and an application specific integratedcircuit (ASIC). The circuitry of sensing module 200 comprisesoperational circuitry 1414, charging circuitry, and power managementcircuitry 1412. The operational circuitry 1414 operates one or moresensing assemblages, controls measurement sequences, processes sensingassemblage data, and transmits information. The power managementcircuitry 1412 operatively couples to circuitry of compact low-powerenergy source 1400 and operational circuitry 1414 to controllably managepower efficiency of the system thereby enabling the use of the capacitor1410 to power sensing module 200 for intra-operative and post-operativemuscular-skeletal parameter measurements.

In one embodiment, the circuitry of sensing module 200 comprises atleast one ASIC. The ASIC comprises the majority of the electronicsystem. The ASIC is architected to operate at low power and providefunctionality to perform sensor measurements. In particular, the ASICincludes power management circuitry 1412, operational circuitry 1414,portions of compact low-energy source 1400, and can include wirelesscommunication circuitry. The ASIC comprises complementary metallic oxidesemiconductor (CMOS) circuitry that is low voltage and low leakage. Thevoltage operation is typically 5 volts or less. Voltage operation ofanalog circuitry can be higher. Digital circuitry can be operated atlower voltages such as 1-3 volts to further reduce power consumption.The ASIC provides a benefit of reduced form factor and low-poweroperation.

The ASIC is further configured in a block architecture. In particular,the operational circuitry 1414 is partitioned in a manner wherebyfunctional blocks can be controlled by the power management circuitry1412. A partitioned block, typically performs a function that isindependent or not reliant on other blocks being operated and therebycan be turned on or off dependent on need to minimize power consumption.In particular, the power management circuitry 1412 can disable or delayoperation of one or more functional blocks to reduce power consumption.In one embodiment, the power management circuitry 1412 makes thesedecisions based on monitoring the charge or voltage on the capacitor.The amount of charge or voltage can be used to determine when a block isenabled. Partitioning circuit components between structures within theintegrated circuit and discrete components enhances design flexibilityand minimizes power consumption without compromising performance.Partitioning functions between analog and digital circuitry alsoenhances design flexibility and facilitate minimizing power consumptionwithout sacrificing functionality or performance.

In a first step, a highly efficient step-up or step-down voltageconverter is implemented in the compact low-power energy source 1400.The step-up or step-down voltage converter circuitry enables essentially“lossless” translation of voltage levels. Further conservation of chargeis achieved through selection of operating voltages and frequencies thatmeet device performance specifications. In a second step, reduction inpower dissipation is achieved by operating circuitry at minimumfrequencies and voltage. The clocking circuitry can be a significantsource of power dissipation. Clock drivers can be optimized toefficiently drive a predetermined load. A clock tree or distributedclocking network can be used. The clock tree distribution is optimizedin conjunction with the clock drivers to minimize delay and maintaintiming at and between distributed nodes providing clock signals. In athird step, the clocked circuitry and the clock frequencies areoptimized for power and sized to assure digital circuit blocks are eachoperated at the optimum clock frequency to achieve required performancewith minimum power consumption.

Disclosed below are further exemplary embodiments to reduce powerconsumption of sensing module 200 that utilizes a temporary powersource. The power management circuitry 1412 places the sensing module200 in one or more power conservation modes depending on a current powerstatus as disclosed below. In general, the ASIC can have multiple inputand output channels. Each channel can have a dedicated function. Forexample, input channels can be used to couple to multiple sensors tomeasure different parameters of the muscular-skeletal system such astemperature, load, or pH. In a fourth step, the input-output channelsare operated such that a single output channel or a single input channelis enabled at any point in time. Thus, the inputs or outputs are enabledsequentially or in sequence and are not operated in parallel to improvepower efficiency. In a fifth step, a single input circuit and a singleoutput circuit is used. This eliminates parallel input or outputoperation. The single input and single output circuit are multiplexed tothe input-output channels. Typically, measurements of themuscular-skeletal system are not time constrained allowing sequentialoperation of the input-outputs to reduce peak power consumption.Furthermore, integrating only the single input circuit and the singleoutput driver reduces the surface area of the integrated circuit as wellas the amount of active circuitry thereby minimizing parasitic leakagepaths.

In a sixth step, the architected design of the ASIC includes matchingsuch that the input-output channels matches the input and outputrequirements of external signals. In the example, specific knowledge ofthe component characteristics is required to provide the match. In oneembodiment, impedance matching produces an efficient energy transferinto and out of the ASIC thereby conserving power. For example, powerefficient matching networks are used for coupling to telemetry, sensors,or transducers. The matching is accomplished with appropriate design ofthe outputs, drivers, and control circuitry within the ASIC that coupleto off-board components and devices. In a seventh step, off-boardsensors and transducers are also operated at optimum frequencies anddrive voltages and currents to achieve the required performance of thewireless module or device at the minimum level of power consumption.Similarly, in an eighth step, operation of all circuit blocks, chargingcircuitry, and telemetry circuitry are each optimized for minimum totalpower consumption to achieve required performance levels. This includes,but is not limited to, timing of off and on states. This is coordinatedto minimize power drain by optimizing timing and duty cycles of allindividual circuit blocks including power drain when powered off pluspower consumption to restart each circuit block versus standby powerconsumption of the separate circuit blocks.

The integration of design methods for ultra low power consumptionachieves outstanding performance with minimum power drain. This enableshighly performing wireless modules or devices powered by a capacitiveenergy storage device including, but not limited to, ultracapacitors,ultra capacitors, super-caps, super capacitors, or other capacitors.Furthermore, the power management circuitry 1412 can operate in one ormore power conservations modes. In a first power conservation mode, thepower management circuitry 1412 can turn off, disable, decouple, ordisconnect circuitry not being used to conserve power. In a second powerconservation mode, the power management circuitry 1412 decouples orturns off the compact low-power energy source 1400 thereby operating onpower from capacitor 1410 when power management circuitry 1410 detectsthat wireless energy source 1402 cannot adequately provide energy or thewireless connection is unstable. In a third power conservation mode, thepower management circuitry 1412 reduces a frequency of operation of oneor more blocks in the ASIC to reduce operating power. In a fourth powerconservation mode, the power management circuitry 1412 disables clockdrivers of a clock tree coupled to circuitry not being used. In a fifthpower conservation mode, the power management circuitry 1412 can placethe operational circuitry in a sleep mode when the circuit is idle for apredetermined time. In a sixth power conservation mode, the powermanagement circuitry 1412 allows parameter measurements to be taken andstored in memory. This can occur when the capacitor 1410 falls below apredetermined threshold. The parameter measurement data is delayed untilto an appropriate time to conserve power. In a seventh powerconservation mode, only a single input or single output of the ASIC isoperated at any time. Finally, an orderly shutdown occurs to preserveparameter measurement data when the power management circuitry 1412detects that the capacitor falls below a predetermined threshold. Ingeneral, the sensing module 200 can be powered by the capacitor 1410 asa result of the power conservation modes and power optimization therebytaking measurements for the duration of a total knee reconstruction.Benefits of the use of capacitors as a power source instead of, or inconjunction with, other power sources or rechargeable technologiesinclude, but are not limited to, enabling a high level ofminiaturization, solid state with no chemistries, almost infinitestorage lifetime, storage with zero charge, quick charge times, andwireless charging.

FIG. 15 is a partial cross-section schematic side view of a sensingplatform 1500 including multiple constructed levels comprisingelectronic substrates with electronic components mounted thereon inaccordance with an exemplary embodiment. In the non-limiting example,the sensing platform is used to measure a force, pressure, or load. Itis a schematic image of components that fit together to make up anassemblage of transducers, interface materials, electrical interconnect,elastic columns, and mechanical structure using multiple electricalsubstrates.

A sensing assemblage comprises energy propagation medium 1516,transducer 1512, and transducer 1514. Energy propagation medium 1516 ispositioned between transducer 1512 and 1514. In a non-limiting example,energy propagation medium 1516 is shaped as a column. Transducers 1512and 1514 emit and detect energy waves that propagate through energypropagation medium 1516. Electronic circuitry coupled to transducers1512 and 1514 detect changes and measure the transit time, frequency, orphase of the propagated energy waves by controlling the timing andduration. In the example, the transit time, frequency, or phase relatesto a force, pressure, or load applied across a top plate 1502 and abottom plate 1504. Typically, the bottom plate 1504 provides aresistance 1510 and the load 1508 is applied to the top plate 1502. Ingeneral, plates 1502 and 1504 provide mechanical support and can provideelectrical interconnect to a transducer.

Flexible interconnect 1506 assures integrity of interconnect whileallowing top plate 1502 to move when load 1508 is applied to thesurface. The elastic strength of energy propagation medium 1516contributes to supporting top plate 1502. The energy propagation mediumfurther maintains a spacing between plates 1502 and 1504. Under a zeroforce or quiescent condition the distance between plates 1502 and 1504are a predetermined distance. The sensing platform 1500 will repeatablyreturn to this predetermined distance under a zero force or quiescentcondition. The distance between plates 1502 and 1504 change as afunction of the load 1508 applied to the top plate 1502. Flexibleinterconnect 1506 provides reliable electrical interconnect to thetransducers 1512 and 1514 without restricting the compression orexpansion of energy propagation medium 1516 or compromising theintegrity of the quantification of the externally applied force,pressure, or load 1508.

In one embodiment, the transducer 1512 contacts an interior surface oftop plate 1502. Similarly, the transducer 1514 contacts an interiorsurface of bottom plate 1504. Transducers 1512 and 1514 are positionedat a predetermined location on the interior surfaces of top plate 1502and bottom plate 1504. The top plate 1502 and the bottom plate 1504 cancomprise an electrically conductive material that can respectively beused as an interconnect to a terminal of transducer 1512 and transducer1514. The flexible interconnect 1506 is routed to make electricalcontact with transducers 1512 and 1514. The upper transducer 1512 orpiezoelectric component has a conductive interface material or materialswhere required, solder or conductive adhesive, for electrical connectionwith flexible interconnect 1506. The lower transducer 1514 orpiezoelectric component has a conductive interface material or materialswhere required, comprising solder or conductive adhesive 1520 forelectrical connection with a second fold or portion of flexibleinterconnect 1506. Note, that the flexible interconnect includes a bend,fold, or arc 1522 to provide interconnect to different locations in thesensing assemblage. In the example, the sensing assemblage forms a stackcomprising top plate 1502, transducer 1512, a first level of flexibleinterconnect 1506, energy propagation medium 1516, a second level offlexible interconnect 1506, transducer 1514, and bottom plate 1504. Inthis configuration, an energy wave couples through the flexibleinterconnect 1506. Moreover, the load 1508 is also applied through theflexible interconnect 1506 as part of the sensing assemblage. Under load1508, the energy propagation medium is the only component of the stackthat changes length.

FIG. 16 is a partial cross-section schematic side view of the sensingplatform 1500 including multiple constructed levels comprisingelectronic substrates with electronic components mounted thereon inaccordance with an exemplary embodiment. The sensing platform 1500 has,in addition to the sensing assemblage or assemblages, printed circuitboards 1612 and 1616. Printed circuit boards 1612 and 1616 are populatedwith electronic components 1610. Electronic components 1610 comprisepower source circuitry, power management circuitry, telemetry, andoperational circuitry for performing parameter measurements. Electroniccomponents 1610 are interconnected by interconnect formed on or withinprinted circuit boards 1612 and 1616. Electronic components 1610 arecoupled to the sensing assemblage by flexible interconnect 1506.

In the embodiment, the sensing assemblage is between top plate 1502 andbottom plate 1504. The example sensing assemblage includes an uppertransducer 1512 positioned in contact with top plate 1502 and a firstside of energy propagation medium 1516. Similarly, the lower transducer1514 is positioned in contact with bottom plate 1504 and a second sideof energy propagation medium 1516. This can include conductive interfacematerial or materials where required, solder or conductive adhesive 1602and 1518 respectively for electrical interconnect with top plate 1502and electrical contact with flexible interconnect 1506. The lowertransducer 1514 has conductive interface material or materials whererequired, solder or conductive adhesive 1608 and 1520 respectively forelectrical interconnect with bottom plate 1504 and with flexibleinterconnect 1506. Solder or conductive adhesive 1608 physically andelectrically connect the components. An upper ground disk 1604 provideselectrical connection between top plate 1502 and flexible interconnect1506. The lower ground disk 1606 provides electrical connection betweenbottom plate 1504 and flexible interconnect 1506. An electrical circuitcomprising electronic components 1610 and the sensing assemblages iscompleted by flexible interconnect 1506 that enables electroniccomponents 1610 to operatively control transducers 1512 and 1514 to emitand detect energy waves into and propagating through energy propagationmedium 1516.

The electronic components 1610 underlie bottom plate 1504. In oneembodiment, bottom plate 1504 is a rigid substrate that isolateselectronic components 1610 from any of the force, pressure, or loadapplied to the sensing platform. Having the one or more sensingassemblages overlying components 1610 provides a compact profile thatallows a sensing module to have a form factor that can be fitted into aprosthetic component for the muscular-skeletal system. At least oneprinted circuit board is used to connect the electronic components 1610.In one embodiment, two printed circuit boards are implemented comprisinga lower electronic circuit board 1616 and an upper electronic circuitboard 1612. The flexible interconnect 1506 is routed to make electricalcontact with the sensing assemblage, upper printed circuit board 1612and lower printed wiring board 1616. The flexible interconnect 1506 isplaced between and electrically connected to printed circuit boards 1612and 1616 at predetermined locations. As mentioned previously, thesensing module can include transmit and receive capability. The sensingmodule can further include an antenna for the wireless communication. Inone embodiment, an integrated antenna 1614 is formed on the lowerprinted circuit board 1616. As shown, the sensing module includes astack of five or more layers of interconnect. The flexible interconnect1506 comprises three levels of interconnect in the stack.

FIG. 17 is a partial cross-section schematic side view of a sensingmodule 1700 including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment. In particular, the sensing module 1700 includesa housing 1706 and a cap 1702. The housing 1706 and cap 1702 form anencapsulating enclosure. The encapsulated enclosure houses sensingassemblages, electronic components, electrical interconnect, andmechanical structure using multiple electrical substrates andencapsulating structure as disclosed herein above. In one embodiment,the encapsulating enclosure is hermetically sealed.

The housing 1706 comprises sidewalls 1716 and a bottom surface 1714.Housing 1706 is made of a rigid material such as polycarbonate that cansupport the force, pressure, or load applied to the sensing module 1700without flexing and is biocompatible. The interior of sidewalls 1716include support features or ledges to suspend components at apredetermined height within housing 1706. Ledges 1708, 1710, and 1712respectively support and retain bottom plate 1504, printed circuit board1612, and printed circuit board 1616. The structures can be attached tothe ledges by mechanical fastener, adhesive, or other attachingmethodology. In one embodiment, the electronic components 1610 onprinted circuit board 1616 face the bottom surface 1714 of housing 1706.The electronic components 1610 mounted on printed circuit board 1612face the bottom plate 1504. The electronic components can be selectedfor each printed circuit board to minimize the combined height therebyreducing the form factor of sensing module 1700.

In one embodiment, an exterior surface of top plate 1502 extends abovean upper surface of sidewalls 1716. The cap 1702 overlies top plate 1502and the upper surface of sidewalls 1716. Cap 1702 includes a lip thatextends over an exterior surface of sidewalls 1716. An adhesive 1704 isplaced between the sidewall 1716 and the lip of cap 1702 to attach andseal the encapsulating enclosure. Thus, the sensing assemblage andelectronic components 1610 are isolated from an external environment. Inthe example, a force, pressure, or load is applied to the exteriorsurface of cap 1702. The force, pressure, or load changes a length ofenergy propagation medium 1516. The change in length over themeasurement range can be small. For example, energy propagation mediumcan change less than 5 millimeters to measure a range of 0 to 100 lbs offorce. In other embodiments, the change in length can be substantiallyless than 5 millimeters depending on the material used for energypropagation medium 1516. The length change corresponds to the movementof cap 1702 and top plate 1502. Thus, cap 1702 and top plate 1502 aremoveable structures in relation to housing 1706. The adhesive 1704 ischosen to allow this movement. For example, a silicone can be used asthe adhesive, which is flexible and allows movement. The silicone willalso seal the encapsulating enclosure. Alternatively, an o-ring can beused in place of adhesive 1706 as a mechanical solution that allowssealed movement. The transit time, frequency, or phase of propagatedenergy waves through medium 1516 is captured by electronic components1610. The transit time, frequency, or phase can be converted to a lengthof energy propagation medium 1516, which is then related to the force,pressure, or load.

A method of electronic assembly is disclosed hereinbelow. The method canbe practiced with more or less than the number of steps shown and is notlimited to the order shown. To describe the method, reference will bemade to the components of FIG. 17, although it is understood that themethod can be implemented in any other manner using other suitablecomponents. In a first step, the conductive interface material ormaterials are positioned in contact with or affixed to planar orconformal surfaces of each piezoelectric resonator or transducer. In asecond step, the sensing assemblage or assemblages, having piezoelectricresonators or transducers 1512 and 1514 and are connected by conductivematerial or materials such as solder, conductive adhesive, conductivepre-forms, or conductive tape 1518, 1520, 1602, 1608 to flexibleinterconnect 1506, top plate 1502, bottom plate 1504, electroniccomponents 1610, upper printed circuit board 1612 and lower printedcircuit board 1616 thereby enabling electrical connection and mechanicalrobustness. Other conductive attaching techniques can be used such asattaching components with double-sided conductive tape or conductiveepoxy. Adhesive tape that conducts electricity in the transversedirection only is another example of a conductive adhesive. Magnesium isan example of a potential interface material.

In a first variation, the flexible interconnect 1506 is routed toprovide additional electrical interconnect to both faces of thetransducers thus eliminating the requirement for multiple uppertransducers or piezoelectric components to share a common electricalconnection. Likewise, the requirement for multiple lower transducers orpiezoelectric components sharing a common electrical connection can beeliminated by routing flexible interconnects to provide electricalcontact to both faces of these components. This would require additionalfolds or segments of flexible interconnect. In a second variation, cap1702 has an external surface that is non-planar or has a conformalsurface. The integration of the non-planar or conformal surface orsurfaces within the structure of the encapsulating enclosure 304 doesnot compromise the protective, hermetic, or mechanical support providedby the enclosure 304. In a third variation, an elastic support betweentop and bottom plates 1502 and 1504 is provided. The elastic supportopposes the force, load, or pressure applied to the sensing module 1700.The elastic support provides greater flexibility in selecting themaximum force, pressure, or load 1508 that is quantified. In a fourthvariation, the transducer 1512 in the sensing assemblage is replacedwith a reflective surface or body and all signals propagating within theenergy propagation medium is emitted and detected by transducer 1514.Using the reflective surface also eliminates top ground disk 1604. In afifth variation, the sensing assemblage is a MEMS, piezo-resistive,mechanical, or strain gauge device coupled to flexible interconnect1506.

FIG. 18 is a cross-sectional view of the sensing module 1700 having asmall form factor in accordance with an exemplary embodiment. In theexample, the external pressure or load can be reliably detected andquantified by the interconnected sensing assemblages and electroniccomponents without direct physical contact. Sensing assemblages 1802comprises one or more transducers and a compressible propagation medium.Detail of the sensing assemblages 1802 is not visible in this view.Electronic components 1610 are affixed to the upper side of the upperprinted circuit board 1612 and the lower side of the printed circuitboard 1616 for mechanical support and electrical interconnect. Theflexible interconnect 1506 couples the individual transducers 1512 and1514 to the electrical components 1610 on the printed wiring boards 1612and 1616 thus enabling complete electrical circuits for electricallystimulating and detecting electrical signals modulated by the energypropagating medium between transducers through the associated column. Inparticular, the illustrations shows two folds of the flexibleinterconnect 1506 that extend in an arc to two different levels offlexible interconnect running through the sensing assemblages 1802 thatin one embodiment is part of the multi-layer interconnect stack.

The encapsulated sensing module or device 1700, as illustrated,comprises the cap 1702 of housing 1706 that encloses the electronicassemblage comprising sensing assemblages, interconnect, and electroniccomponents. The top plate 1502 transfers flexor with changes in load1508 of the load-bearing surface of the cap 1702 to the sensing elementsof the sensing assemblages 1802. Mechanical support for electrical andmechanical components within the encapsulated sensing module 1700 isprovided by features, ledges, and structures designed into the walls ofthe housing 1706.

FIG. 19 is a perspective view of the interconnect stack of the sensingmodule 1700 in accordance with an exemplary embodiment. In theembodiment, three assemblages 1802 couple to predetermined positions ofthe top plate 1502 (not shown). Multiple sensing assemblages 1802 areused to measure the force, pressure, or load and to identify where onthe top plate 1502 (not shown) the parameter was applied. The locationwhere the parameter is applied is determined by the magnitudes measuredby each sensing assemblage 1802, the differential between themeasurements, and the location where each sensing assemblage couples totop plate 1502 (not shown). The sensing module 1700 illustrates flexibleinterconnect supporting electronic components within the sensingassemblage or assemblages 1802. A single flexible interconnect comprisesthree levels of interconnection in the interconnect stack. A first level1806 of the flexible interconnect is shown coupling between thetransducers 1512 and corresponding energy propagation medium 1516. Thefirst level of flexible interconnect 1806 includes a fold, bend, or arc1812 that connects to a third level 1810 of the flexible interconnect. Asecond level 1808 of the flexible interconnect is shown coupling betweenenergy propagation medium 1516 and the lower transducer 1514 (notshown). The second level 1808 of the flexible interconnect includes anarc 1804 that connects to the third level 1810 of the flexibleinterconnect. Note that both the first level 1806 and the second level1808 includes interconnect that respectively connects to the threetransducers 1512 and 1514. The third level 1810 of the flexibleinterconnect 1506 is between and connected to printed circuit boards1612 and 1616. The printed circuit boards 1612 and 1616 includeoperational circuitry that couple to the sensing assemblages 1802 togenerate parameter measurements from each sensing assemblage 1802. Theupper and lower printed circuit, boards 1612 and 1616, flexibleinterconnect 1506, electronic components 1610, and bottom plate 1504illustrate the spatial and mechanical relationships among the electricalsubstrates. The bottom plate 1504 is between the sensing assemblages1802 and the electronic components 1610. It should be noted that in theembodiment, the flexible interconnect is part of the transmission pathof the sensing assemblage. Energy waves transmit through the flexibleinterconnect into the energy propagation medium 1516. Similarly,propagated energy waves exiting the energy propagation medium 1516transmit through the flexible interconnect to be detected by atransducer.

FIG. 20 is a partial cross-section schematic side view of a sensingplatform 2000 including multiple constructed levels comprisingelectronic substrates with electronic components mounted thereon inaccordance with an exemplary embodiment. It is a schematic image ofcomponents that fit together to comprise an integrated assemblage havinga sensor 2002 attached to flexible electrical interconnect 1506 andsupported by top plate 1502 and bottom plate 1504 within anencapsulating enclosure as described hereinabove. The sensor 2002replaces the sensing assemblage comprising transducer 1512, energypropagation medium 1516, and transducer 1514 shown in FIG. 15. In theembodiment, a thin film piezo-resistive sensor is used as sensor 2002 tomeasure the applied force, pressure, or load 1508. Piezo-resistivepressure sensors typically comprise a layer of pressure sensitive inksandwiched between two conductive layers. The combination of conductivelayers and pressure sensitive ink is encapsulated in a flat package withleads typically extending from a sidewall of the sensor. Sensor 2002 canhave a thin form factor that reduces a height of the sensing module.Furthermore, piezo-resistive sensor 2002 is shaped in a manner thatallows interconnect stacking. The sensor 2002 has a low level ofconductance under a quiescent condition when no force, pressure, or loadbeing applied to the piezo-resistive film. The quiescent condition canalso be at a predetermined force, pressure, or load depending on theapplication. Applying a force, pressure, or load to the piezo-resistivefilm applies pressure to the ink layer. In the embodiment, the force,pressure, or load applied to top plate 1502 compresses the sensor 2002.The pressure on the ink increases the conductance as conductiveparticles are forced in contact or in proximity to each other. The moretightly they are compressed, the lower the resistance of sensor 2002.Conversely, as pressure is removed, the resistance of sensor 2002returns to its quiescent state. The sensing platform 2000 can include anelastic structure (not shown) that returns the top plate to a preciseposition in relation to bottom plate 1504 after the force, pressure, orload is removed.

In one embodiment, the piezo-resistive sensing assemblage is a stackthat comprises a load disk 2004, adhesive layer 2006, sensor 2002, andan adhesive layer 2008. The load disk 2004 is a spacer or column that isnon-compressible or inelastic. The load disk 2004 can have a majorsurface that evenly distributes the force, pressure, or load across themajor surface sensor 2002. The major surface of the load disk 2004 has apredetermined area for contacting the sensor 2002. Adhesive layer 2006is non-conductive tape, adhesive, or other securing means that attachesload disk 2004 to sensor 2002. In the embodiment, the load disc 2004 ispositioned respectively between top plate 1502 and bottom plate 1504.Adhesive layer 2008 is non-conductive tape, adhesive, or other securingmeans that attaches sensor 2002 to bottom plate 1504. Top plate 1502transmits the level of force, pressure, or load 1508 externally appliedto the top surface (not shown) of the encapsulated enclosure (notshown). The load disk 2004 then couples load 1508 from top plate 1502 tosensor 2002. The bottom plate 1504 is rigidly supported, through themechanical structure of the encapsulating enclosure to maintainresistance 1510 to movement thereby enabling accurate quantification ofthe externally applied force, pressure, or load 1508.

In one embodiment, sensor 2002 has interconnect 2010 and 2012 thatextends form the sidewall of the device. Interconnect 2010 and 2012 isconnected to flexible interconnect 1506. Alternatively, sensor 2002 canhave electrical contact terminals on either or both major surfaces thatreceive loading. In this embodiment, flexible interconnect 1506 would bepart of the sensing assemblage stack between upper tape 2006, lower tape2008, and sensor 2002 to make one or more connections. Moreover, theflexible interconnect 1506 would receive loading 1508 as part of thesensing assemblage. Current flow through upper interconnect 2010, sensor2002, and lower interconnect 2012 is modulated by changes in force,pressure, or load 1508. This current flow is carried through traces onthe surface of flexible interconnect 1506 to electronic circuitry (notshown) within the sensing module. Flexible interconnect 1506 providesreliable electrical interconnect to the one or more piezo-resistivesensing assemblages without restricting the transmission or compromisingthe integrity of the force, pressure, or load 1508 applied to thesensing module. In general, thin film piezo-resistive pressure sensorshave benefits of simplicity, cost, power, form factor when compared toother sensing technologies. Interfacing with sensor 2002 andinterpreting measurement data can reduce both mechanical and circuitryrequirements thereby providing further benefit.

FIG. 21 is a partial cross-section schematic side view of the sensingplatform 2000 including multiple constructed levels comprisingelectronic substrates with electronic components mounted thereon inaccordance with an exemplary embodiment. The sensing platform 2000 has,in addition to the sensing assemblage or assemblages, printed circuitboards 1612 and 1616. Printed circuit boards 1612 and 1616 are populatedwith electronic components 1610. Electronic components 1610 comprisepower source circuitry, power management circuitry, telemetry, andoperational circuitry for performing parameter measurements. Electroniccomponents 1610 are coupled to the sensing assemblage by flexibleinterconnect 1506. In one embodiment, using sensor 2002 in the sensingassemblage requires four layers of electrical interconnect.

The electronic components 1610 underlie bottom plate 1504 (not shown).In one embodiment, bottom plate 1504 is a rigid substrate that isolateselectronic components 1610 from any of the force, pressure, or loadapplied to the sensing platform. Having the one or more sensingassemblages overlying components 1610 provides a compact profile thatallows a sensing module to have a form factor that can be fitted into aprosthetic component for the muscular-skeletal system. At least oneprinted circuit board is used to connect the electronic components 1610.In one embodiment, two printed circuit boards are implemented comprisinga lower electronic circuit board 1616 and an upper electronic circuitboard 1612. The flexible interconnect 1506 is routed to make electricalcontact with the sensing assemblage, upper printed circuit board 1612and lower printed wiring board 1616. The electronic components 1610detect and digitize changes in levels of the conductance of thin filmpiezo-resistive sensor 2002. The measured value of conductance can beconverted to a force, pressure, or load value. The flexible interconnect1506 is placed between and electrically connected to printed circuitboards 1612 and 1616 at predetermined locations. As mentionedpreviously, the sensing module can include transmit and receivecapability. The sensing module can further include an antenna 1614 forthe wireless communication. In one embodiment, the antenna 1614 isformed on the lower printed circuit board 1616. The antenna is aconductive trace on the printed circuit board 1616 formed in loop aroundthe periphery. As shown, the sensing module includes a stack of fourlayers of interconnect. The flexible interconnect 1506 comprises hasconnections at two levels of interconnect in the stack.

FIG. 22 is a partial cross-section schematic side view of a sensingmodule 2200 including multiple constructed levels comprising electronicsubstrates with electronic components mounted thereon in accordance withan exemplary embodiment. In particular, the sensing module 2200 includesa housing 1706 and a cap 1702. The housing 1706 and cap 1702 form anencapsulating enclosure. The encapsulated enclosure houses sensingassemblages, electronic components, electrical interconnect, andmechanical structure using multiple electrical substrates andencapsulating structure as disclosed herein above. In one embodiment,the encapsulating enclosure is hermetically sealed.

The housing 1706 comprises sidewalls 1716 and a bottom surface 1714.Housing 1706 is made of a rigid material such as polycarbonate that cansupport the force, pressure, or load applied to the sensing module 1700without flexing and is biocompatible. The interior of sidewalls 1716include support features or ledges to suspend components at apredetermined height within housing 1706. Ledges 1708, 1710, and 1712respectively support and retain bottom plate 1504, printed circuit board1612, and printed circuit board 1616. In addition, support structurescan be coupled from the bottom surface of housing 1706 for furthersupport or as an option to the ledges. The structures can be attached tothe ledges by mechanical fastener, adhesive, or other attachingmethodology. In one embodiment, the electronic components 1610 onprinted circuit board 1616 face the bottom surface 1714 of housing 1706.The electronic components 1610 mounted on printed circuit board 1612face the bottom plate 1504. The electronic components can be selectedfor each printed circuit board to minimize the combined height therebyreducing the form factor of sensing module 1700.

In one embodiment, an exterior surface of top plate 1502 extends abovean upper surface of sidewalls 1716. The cap 1702 overlies top plate 1502and the upper surface of sidewalls 1716. Cap 1702 includes a lip thatextends over an exterior surface of sidewalls 1716. An adhesive 1704 isplaced between the sidewall 1716 and the lip of cap 1702 to attach andseal the encapsulating enclosure. Thus, the sensing assemblage andelectronic components 1610 are isolated from an external environment. Inthe example, a force, pressure, or load is applied to the exteriorsurface of cap 1702. The force, pressure, or load is applied through topplate 1502 and load disk 2004 to sensor 2002. The housing 1706 andbottom plate 1504 provide a resistance against the force, pressure, orload thereby compressing the sensor 2002. The applied force, pressure,or load to the piezo-resistive film of sensor 2002 results in acorresponding change in resistance of the film. The electroniccomponents 1610 couple to sensor 2002 through flexible interconnect 1506forming a sensing circuit that detects a change in current or voltage asa result of a resistance change in the piezo-resistive material. Themeasured current or voltage directly corresponds to the force, pressure,or load. The measurement be stored in memory or transmitted. It shouldbe noted that the applied force, pressure or load causes movement of cap1702 and top plate 1502. Thus, both are moveable structures in relationto housing 1706. The adhesive 1704 is chosen to allow this movement. Forexample, a silicone can be used as the adhesive, which is flexible andallows movement. The silicone will also seal the encapsulatingenclosure. An o-ring could also be used in place of adhesive 1706 as amechanical solution.

FIG. 23 is a perspective view 2300 of an exemplary loop antenna 2302 inaccordance with one embodiment. As shown, the loop antenna 2302 isintegrated along a periphery of the medical device to maximize theantenna trace length and exposure. In such an arrangement, the loopantenna 2302 radiates energy outwards along the circumference of thesensing module thereby enabling low-power operation when used inconjunction with a receiver placed in the vicinity of the sensingmodule. For instance, in the context of a load sensing insert device 100used in knee implant surgery, the outer periphery is closest to theoutside of the knee where a receiver device can be placed on the skin toscan the sensing module 200 for communication data. In thisillustration, the loop antenna 2302 forms one or more loops along theoutermost periphery of the encapsulated sensing module 200 as permittedby the encapsulated printed circuit board or electronic packagingsubstrate. A port 2304 includes two terminals that serve to couple theloop antenna 2302 to electronic components of the sensing module 200,such as the transceiver 320. The port 2304 can also couple external tothe sensing module 200. The port 2304 couples to communication circuitrywithin the sensing module 200 and an antenna. In one embodiment, amatching network can be placed between transceiver 320 and antenna 2302to improve efficiency. In an alternative embodiment, the loop antenna2302 is formed on a flexible interconnect instead of a printed circuitboard within the sensing module 200. The flexible interconnect couplesthe antenna 2302 to the communication circuitry and can include a bendthat positions the loop antenna 2302 appropriately within the sensingmodule for transmission of data.

In another embodiment, the loop antenna 2302 is electrically coupled tothe insert dock 202. The insert dock 202 is larger than sensing module200 and has a larger peripheral area. A longer conducting antenna loopis formed in, on, or around the insert dock 202 for radio frequencycommunication. As an example, the insert dock 202 includes electricalwiring to serve as the loop antenna 2302. A hermetically sealedcommunications port resides on sensing module 200. As mentioned, theport 2304 couples to the communication circuitry and can be external tothe sensing module 200. In one embodiment, port 2304 couples to thematching network. The external communication port on sensing module 200connects to a corresponding port on the insert dock when inserted. Theport or terminals on insert dock 202 connect to the antenna loop in oron the insert dock 202. In yet another arrangement, the insert dock 202can comprise metal for being a conductor of radio communications.

FIG. 24 is a perspective view 2400 of an integrated loop antenna 2402according to another embodiment. As illustrated, the integrated loopantenna 2402 is integrated into a substrate of a printed circuit board2406 of the sensing insert device 100. Other embodiments are not limitedto the illustrated loop, or similarly shaped or functioning integratedloop antennas. As shown, the integrated loop antenna 2402 comprisescircuit traces 2404 on a top (or bottom) layer of the substrate of thecircuit board 2406. The traces 2404 act as a portion of the radiatingand receiving body of the integrated loop antenna 2402. The circuitboard 2406 can comprise multiple interconnect layers that can be formedas part of the radiating and receiving body, counterpoise, reflectors,or other structural components of the antenna 2402. The circuit traces2404 can be etched to navigate around other electrical components andeven the edge of the circuit board in certain embodiments.

Printed circuit technology supports the creation of many shapes ofconductors and conducting surfaces on each layer of a multi-layercircuit board or flexible substrate. These conductors and conductingsurfaces may be arranged and interconnected to function as radiating orreceiving, reflection, and other surfaces of an integrated antenna. Theconductors and conducting surfaces on each individual layer of thesubstrate may be interconnected in a variety of configurations.Conductors and conducting surfaces on each layer of the substrate mayalso be connected with conductors and conducting surfaces on otherlayers in a variety of configurations. This provides flexibility todesign and integrate many forms of antennas with different radiationpatterns, polarizations, frequency ranges, levels of Q, and impedancecharacteristics.

The circuit board 2406 comprises a matching network A, a radio frequencyoutput stage B, and optional receiver circuit C. These block diagramcomponents are functionally related to the transceiver 320 andelectronic circuitry 307 of FIG. 5. The block models can comprise analogcomponents, digital components, discrete components, integrated circuitcomponents or any combination thereof. As shown, the circuitry ismounted on circuit board 2406. The matching network A provides impedancematching to an external receiver communications network to provideoptimal power efficiency. The radio frequency output stage B drives thematching network A. The radio frequency output stage B amplifies andtransmits communication signals to an external receiver. In the example,the communication signal will carry information that includes parametermeasurement data such as load and balance measurements. The receivercircuit C is an optional component that can be integrated by way ofswitching (e.g., a Transmit-Receive (TR) switch) to receive datacommunications from an external transmitter, for example, to download aserial number.

The integration of the antenna 2402 into a rigid or flexible substratefor electronic circuits enables highly compact Radio Frequency (RF)modules, devices, instruments, or equipment with adequate radiatingefficiency to operate at low power levels in many short-rangeapplications. Integrated antennas have adequate receiving sensitivityfor many of these applications as well. In one embodiment, the transmitpower in conjunction with the loop antenna 2402 can be designed to limitthe transmission distance. For example, it can restrict communicationtransmission to a distance corresponding to an operating room, doctor'soffice, or patient home thereby preventing or deterring others fromreceiving the measurement data. In one embodiment, the sensing module200 is in an implant that would underlie tissue and portions of themuscular-skeletal system. In the embodiment, a portable receiver wouldbe placed near the implant to receive or transmit information to thesensing module. These wireless modules, devices, instruments, orequipment may be constructed using high volume, low cost, standardmanufacturing processes thus producing high quality, high reliability,deeply miniaturized radio frequency transmitter or receiver modules,devices, instruments, or equipment.

Integration of the antenna 2402 within the electronic assembly enablesthe construction of compact wireless equipment. In addition to a widerange of short-range handheld, wearable, or other portable communicationequipment, many applications may also include data measurement,collection, and communication modules, devices, or equipment for a widerange of applications. Additional potential applications may include,but are not limited to, a wide range of medical applications. Potentialmedical applications may include, but are not limited to,intra-operative medical devices, trial inserts, and implants, othershort-term medical devices, including devices that are inserted oringested, other implanted medical devices, wearable medical devices,handheld devices, disposable medical devices or modules, medicalinstruments, medical equipment, accessories for medical instruments andequipment, and disposables associated with medical instruments,equipment, accessories.

FIG. 25 Illustrates by way of example, a plot 2500 of normalizedradiated field strength 2502 versus frequency 2504 performance of anexample loop antenna integrated into a rigid or flexible substrate ofthe electronic circuit board. The plot 2500 illustrates radiationefficiency of the antenna and matching network from a circuit analysis.By way of electronic circuitry 307, the loop antenna can be configuredto produce a frequency of maximum power output 2506. The electroniccircuitry can further shape the peak (or radiation pattern) via a tuningmechanism to narrow (broaden) the peak and the relative Q level of theantenna. As one example, the electronic circuitry can emit a beaconsignal over a broad frequency span, and upon receiving a ping for aparticular communication channel, self-configure to narrow the peak toreceive further communications under optimal power communicationsettings.

FIG. 26 Illustrates a radiation pattern of the loop antenna integratedinto a flexible substrate of an electronic circuit in accordance with anexemplary embodiment. The axes of the null points are readily visibleand indicate that direction performance of reception and transmissioncan be well suited to applications where directional communicationsminimize the potential for inference. For instance, in the currentantenna layout pattern, wherein the loop antenna is along an outerperiphery, a radiation pattern is generated in a shape that propagatesaway from the implant site and in a direction, which facilitatesacceptable signal to noise ratio (SNR). As shown, the null radiationlobes 2604 of the antenna pattern 2602 can be seen at positions where itmay be less practical to place the receiver (e.g., along the femur ortibial axis), and that higher radiation lobes (or patterns) 2606 of theantenna pattern 2602 are along the outside periphery of the implant andare closest to the patient skin surface where a receiver can be placed.In other embodiments, the loop antenna can be physically configured, andin conjunction with control circuitry, to indicate a strong directionalpattern of preferred reception and transmission thus making oneparticular instance of an integrated loop antenna well suited toapplications that require omni-directional communications.

FIG. 27 illustrates a low power consumption integrated transducer drivercircuit 2700 in accordance with an exemplary embodiment. In a firstembodiment, driver circuit 2700 efficiently drives a transducer togenerate time and frequency specific energy waves and pulses. Itincludes digital logic to generate drive signals according to thetransducer characteristics and operational modes to achieve highlyaccurate control, timing, and duration of the generated energy waves andpulses. In one arrangement, the output driver is coupled to anultrasonic sensing assembly to efficiently generate continuousultrasonic waves or ultrasonic pulses that propagate through apropagation medium. The driver circuit includes a level shifter 2712 toraise or lower voltage levels of output pulses to voltage levelsrequired to efficiently drive an energy emitting resonator or transducergiven the characteristics of the resonator or transducer, the frequencyand duration of the output waves, and the shape of the output pulse. Itincludes an impedance matching network 2714 to translate the digitaloutput pulse into a required wave shape for efficiently and compactlydriving the transducer. This configuration provides the benefit forbattery or temporarily powered sensing systems to drive the energyemitting resonators or transducers with much less power consumption thana Digital to Analog Converter (DAC) based design.

In a second embodiment, the driver circuit 2700 is incorporated within apropagation tuned oscillator (PTO) to maintain positive closed-loopfeedback. The PTO can operate in continuous wave mode, pulse-loop mode,pulse-echo mode, or controlled combination thereof. The driver circuit2700 is electrically integrated with the PTO by multiplexing input andoutput circuitry, including off-board components of an impedancematching network, to achieve ultra low-power and small compact size. Inthis arrangement, off-board energy emitting resonators or transducersare operated at optimum frequencies and drive voltages and currents toachieve optimal performance at a minimum level of power consumption. Thedrive circuit 2700 can singly drive multiple energy emitting resonatorsor transducers to achieve this level of performance; that is, only onedriver circuit can be shared. Appropriate duty cycles and multiplexingtiming for optimum frequencies of the energy emitting resonators ortransducers are selected to conserve both power and space withoutcompromising performance. This enables, but is not limited to, thedesign and construction of compact measurement modules or devices withthickness on the order of a few millimeters.

In one embodiment, low power consumption transducer driver circuit 2700comprises control logic 2708, a digital driver 2706, level shifter 2712,an amplifier 2716, and matching network 2714. The driver circuit 2700can be implemented in discrete analog components, digital components, anapplication integrated circuit, or a combination thereof. In a low powerapplication, transducer driver circuit 2700 is integrated with othercircuitry of the propagation tuned oscillator. Briefly, the transducerdriver circuit 2700 accurately controls emissions of energy waves orpulses, and parameters thereof, including, but not limited to, transittime, phase, or frequency of the energy waves or pulses. A briefdescription of the method of operation is as follows.

An input 2702 receives a signal to emit an energy wave. Input 2702couples to control logic 2708. Control logic 2708 controls the timingand frequency of stimulation of an energy transducer 2710. A digitalpulse 2704 from digital control logic 2708 is provided to an input ofdriver 2706. In an energy pulse mode, digital control logic 2708 alsocontrols the duration of the stimulation. One or more pulses from anoutput 2718 of driver 2706 are coupled to level shifting circuitry 2712.Level shifting circuitry 2712 adjusts the output voltage of driver 2706to efficiently drive energy transducer 2710. One or more level shiftedpulses are provided at an output 2720 of level shifter 2712 to amplifier2716. Amplifier 2716 amplifies the signal at output 2720, which isprovided, to an input of matching network 2714. Matching network 2714matches the electrical characteristics of the energy transducer 2710.The output signal 2722 from the matching network 2714 enables energytransducer 2710 to emit an energy wave. Matching network 2714 convertsthe output pulse from amplifier 2716 to the required wave shape,frequency and phase. Transducer 2710 emits energy waves 2724 into themedium upon excitation by the signal output from matching network 2714.

As discussed above, the electronic components are operatively coupled asblocks of integrated circuits. As will be shown ahead, this integratedarrangement performs its specific functions efficiently with a minimumnumber of components. A portion of the efficiency is achieved becausethe circuit components are partitioned between structures within anintegrated circuit and discrete components, as well as innovativepartitioning of analog and digital functions, to achieve the requiredperformance with a minimum number of components and minimum powerconsumption.

Briefly, an input of digital driver 2706 is driven by digital controllogic 2708, which ultimately controls the timing and frequency of theresulting output signal 2722. As will be shown ahead, the output signal2722 drives an energy transducer 2710 to output an energy wave or energypulse. The drive circuit 2700 is optimally configured to generate theoutput signal 2722 according to the transducer characteristics (e.g.,frequency, stiffness, Q, ringing, inductance, ringing, decay, feedback)and in certain cases the operating mode (e.g., continuous, pulse-loop,and pulse echo). For example, in pulse-loop mode, digital control logic2708 also controls the duration of the transducer 2710 stimulation.Level shifter 2712 adjusts the output voltage of driver output 2706 toefficiently drive energy transducer 2710. More specifically, the levelshifter 2712 raises or lowers voltage levels of output pulses to thevoltages required to efficiently drive the energy emitting resonator ortransducer 2710 given the characteristics of the resonator or transducer2710, the frequency and duration of the output waves, and the shape ofthe output pulse. Matching network 2714 matches the electricalcharacteristics of the energy transducer 2710 and converts the outputpulse 2722 to the required wave shape, frequency and phase. Thegenerated digital output waveform 2722 or pulse may have a moderatelysharp leading edge.

With regard to the integrated transducer driver 2700, efficient use ofpower and conservation of charge is required for ultra low poweroperation. Energy emitting resonators or transducers 2710 can bestimulated with a sine wave or other form of continuous wave toefficiently emit energy waves of the required frequency, phase, andduration. Partitioning circuit components between structures within theintegrated circuit and discrete components enhances design flexibilityand minimize power consumption without compromising performance.Therefore, the driver circuit 2700 and matched network 2714 togetherefficiently convert the input pulse 2704 to an energy wave 2724 of therequired frequency, phase, and duration, which is specific to operationof transducer 2710.

The output of the driver amplifier 2716 is coupled with the impedancematching network 2714, such as, but not limited to, a pi network. Thispi network can include a discrete inductor or inductors and a discretecapacitor or capacitors to translate the digital output pulse into therequired wave shape efficiently and compactly. In one arrangement, thephase and time delay through the pi network are constant. The pi networkmay also include resistance as well as the discrete inductance andcapacitance components. The resistance element is included in theanalysis and comprises parasitic resistances within the integratedcomponents and interconnects of the circuit. They are included in theanalysis and design of the pi network to assure matching the electricaldrive requirements of the energy emitting device.

The impedance matching network 2714 generates a waveform 2722 that isoptimized for emitting resonator or transducer 2710. The network 2714drives the energy emitting resonators or transducers 2710 efficientlythereby reducing power consumption. In particular, the power consumptionis substantially less than using an equivalent Digital to AnalogConverter (DAC) based design. The integration of miniature, surfacemountable, inductors and capacitors enables highly compact drivercircuit and minimizes the total number of electronic components. In ahybrid approach, off-chip and return to on-chip, may have size penaltybut can be integrated to save power and reduce design complexity.

FIG. 28 illustrates a block diagram of an edge-detect receiver circuit2800 in accordance with an exemplary embodiment. In a first embodiment,edge-detect receiver 2800 is provided to detect wave fronts of energywaves. This enables capturing of parameters including, but not limitedto, transit time, phase, or frequency of the energy waves. Circuitry ofthe integrated edge-detect receiver 2800 provides rapid on-set detectionand quickly responds to the arrival of an energy wave. It reliablytriggers thereafter a digital output pulse at a same point on theinitial wave front of each captured energy wave or pulsed energy wave.The digital pulse can be optimally configured to output with minimal andconstant delay. The edge-detect receiver 2800 can isolate and preciselydetect the specified point on the initial energy wave or the wave frontin the presence of interference and distortion signals therebyovercoming problems commonly associated with detecting one of multiplygenerated complex signals in energy propagating mediums. The edge-detectreceiver 2800 performs these functions accurately over a wide range ofamplitudes including very low level energy pulses.

In a second embodiment, the edge-detect receiver 2800 is incorporatedwithin a propagation tuned oscillator (PTO) to maintain positiveclosed-loop feedback when operating in a continuous wave, pulse orpulse-echo mode. The edge-detect receiver 2800 can be integrated withother circuitry of the PTO by multiplexing input and output circuitry toachieve ultra low-power and small compact size. Integration of thecircuitry of the PTO with the edge-detect receiver provides the benefitof increasing sensitivity to low-level signals.

The block diagram illustrates one embodiment of a low power edge-detectreceiver circuit 2800 with superior performance at low signal levels.The edge-detect receiver 2800 comprises a preamplifier 2812, adifferentiator 2814, a digital pulse circuit 2816 and a deblank circuit2818. The edge-detect receiver circuit 2800 can be implemented indiscrete analog components, digital components or combination thereof.In one embodiment, edge-detect receiver 2800 is integrated into an ASICas part of a sensor system described hereinbelow. The edge-detectreceiver circuit 2800 practices measurement methods that detect energypulses or pulsed energy waves at specified locations and under specifiedconditions to enable capturing parameters including, but not limited to,transit time, phase, frequency, or amplitude of energy pulses. A briefdescription of the method of operation is as follows. In a non-limitingexample, a pre-amplifier triggers a comparator circuit responsive tosmall changes in the slope of an input signal. The comparator and otheredge-detect circuitry responds rapidly with minimum delay. Detection ofsmall changes in the input signal assures rapid detection of the arrivalof a pulse of energy waves. The minimum phase design reduces extraneousdelay thereby introducing less variation into the measurement of thetransit time, phase, frequency, or amplitude of the incoming energypulses.

An input 2820 of edge-detect receiver 2800 is coupled to pre-amplifier2812. As an example, the incoming wave 2810 to the edge-detect receivercircuit 2800 can be received from an electrical connection, antenna, ortransducer. The incoming wave 2810 is amplified by pre-amplifier 2812,which assures adequate sensitivity to small signals. Differentiatorcircuitry 2814 monitors the output of pre-amplifier 2812 and triggersdigital pulse circuitry 2816 whenever a signal change corresponding toan energy wave is detected. For example, a signal change that identifiesthe energy wave is the initial wave front or the leading edge of theenergy wave. In one arrangement, differentiator 2814 detects currentflow, and more specifically changes in the slope of the energy wave 2810by detecting small changes in current flow instead of measuring changesin voltage level to achieve rapid detection of slope. Alternatively,differentiator 2814 can be implemented to trigger on changes in voltage.Together, preamplifier 2812 and differentiator 2814 monitor thequiescent input currents for the arrival of wave front of energy wave(s)2810. Preamplifier 2812 and differentiator 2814 detect the arrival oflow level energy waves as well as large magnitude energy waves. Thisdetection methodology achieves superior performance for very low levelsignals. Differentiator circuitry 2814 triggers digital pulse circuitry2816 whenever current flow driven by the initial signal ramp of theincoming wave 2810 is detected. The digital pulse is coupled to deblankcircuit 2818 that desensitizes pre-amplifier 2812. For example, thedesensitization of pre-amplifier 2812 can comprise a reduction in gain,decoupling of input 2820 from energy wave 2810, or changing thefrequency response. The deblank circuit 2818 also disregards voltage orcurrent levels for a specified or predetermined duration of time toeffectively skip over the interference sections or distorted portions ofthe energy wave 2810. In general, energy wave 2810 can comprise morethan one change in slope and is typically a damped wave form if theenergy wave is pulsed. Additional signals or waves of the pulsed energywave on the input 2820 of pre-amplifier 2812 are not processed duringthe preset blanking period. In this example, the digital output pulse2828 can then be coupled to signal processing circuitry as explainedhereinbelow. In one embodiment, the electronic components areoperatively coupled as blocks within an integrated circuit. As will beshown ahead, this integration arrangement performs its specificfunctions efficiently with a minimum number of components. This isbecause the circuit components are partitioned between structures withinan integrated circuit and discrete components, as well as innovativepartitioning of analog and digital functions, to achieve the requiredperformance with a minimum number of components and minimum powerconsumption.

FIG. 29 is a block diagram of a zero-crossing receiver 2900 inaccordance with one embodiment. In a first embodiment, the zero-crossingreceiver 2900 is provided to detect transition states of energy waves,such as the transition of each energy wave through a mid-point of asymmetrical or cyclical waveform. This enables capturing of parametersincluding, but not limited to, transit time, phase, or frequency of theenergy waves. The receiver rapidly responds to a signal transition andoutputs a digital pulse that is consistent with the energy wavetransition characteristics and with minimal delay. The zero-crossingreceiver 2900 further discriminates between noise and the energy wavesof interest, including very low level waves by way of adjustable levelsof noise reduction. A noise reduction section 2918 comprises a filteringstage and an offset adjustment stage to perform noise suppressionaccurately over a wide range of amplitudes including low level waves.

In a second embodiment, a zero-crossing receiver 2900 is provided toconvert an incoming symmetrical, cyclical, or sine wave to a square orrectangular digital pulse sequence with superior performance for verylow level input signals. The digital pulse sequence represents pulsetiming intervals that are consistent with the energy wave transitiontimes. The zero-crossing receiver 2900 is coupled with a sensingassembly to generate the digital pulse sequence responsive to evaluatingtransitions of the incoming sine wave. This digital pulse sequenceconveys timing information related to parameters of interest, such asapplied forces, associated with the physical changes in the sensingassembly.

In a third embodiment, the integrated zero-crossing receiver isincorporated within a propagation tuned oscillator (PTO) to maintainpositive closed-loop feedback when operating in a continuous wave mode,pulse mode, or pulse-echo mode. The integrated edge zero-crossingreceiver is electrically integrated with the PTO by multiplexing inputand output circuitry to achieve ultra low-power and small compact size.Electrical components of the PTO are integrated with components of thezero-crossing receiver to assure adequate sensitivity to low-levelsignals.

In one embodiment, low power zero-crossing receiver 2900 can beintegrated with other circuitry of the propagation tuned oscillator tofurther improve performance at low signal levels. The zero-crossingreceiver 2900 comprises a preamplifier 2906, a filter 2908, an offsetadjustment circuitry 2910, a comparator 2912, and a digital pulsecircuit 2914. The filter 2908 and offset adjustment circuitry 2910constitute a noise reduction section 2918 as will be explained ahead.The zero-crossing receiver 2900 can be implemented in discrete analogcomponents, digital components or combination thereof. The integratedzero-crossing receiver 2900 practices measurement methods that detectthe midpoint of energy waves at specified locations, and under specifiedconditions, to enable capturing parameters including, but not limitedto, transit time, phase, or frequency of energy waves. A briefdescription of the method of operation is as follows.

An incoming energy wave 2902 is coupled from an electrical connection,antenna, or transducer to an input 2904 of zero-crossing receiver 2900.Input 2904 of zero-crossing receiver 2900 is coupled to pre-amplifier2906 to amplify the incoming energy wave 2902. The amplified signal isfiltered by filter 2908. Filter 2908 is coupled to an output ofpre-amplifier 2906 and an input of offset adjustment circuitry 2910. Inone configuration, filter 2908 is a low-pass filter to remove highfrequency components above the incoming energy wave 2902 bandwidth. Inanother arrangement, the filter is a band-pass filter with a pass-bandcorresponding to the bandwidth of the incoming energy wave 2902. It isnot however limited to either arrangement. The offset of the filteredamplified wave is adjusted by offset adjustment circuitry 2910. An inputof comparator 2912 is coupled to an output of offset adjustmentcircuitry 2910. Comparator 2912 monitors the amplified waveforms andtriggers digital pulse circuitry 2914 whenever the preset trigger levelis detected. Digital pulse circuit 2914 has an input coupled to theoutput of comparator 2912 and an output for providing digital pulse2916. The digital pulse 2916 can be further coupled to signal processingcircuitry, as will be explained ahead.

In a preferred embodiment, the electronic components are operativelycoupled together as blocks of integrated circuits. As will be shownahead, this integrated arrangement performs its specific functionsefficiently with a minimum number of components. This is because thecircuit components are partitioned between structures within anintegrated circuit and discrete components, as well as innovativepartitioning of analog and digital functions, to achieve the requiredperformance with a minimum number of components and minimum powerconsumption.

FIG. 30 is a sensor interface diagram incorporating the zero-crossingreceiver 2900 in a continuous wave multiplexing arrangement formaintaining positive closed-loop feedback in accordance with oneembodiment. The positive closed-loop feedback is illustrated by the boldline path. Initially, multiplexer (mux) 3002 receives as input a clocksignal 3004, which is passed to the transducer driver 2700 to producethe drive line signal 3008. Analog multiplexer (mux) 3010 receives driveline signal 3008, which is passed to the transmitter transducer 3012 togenerate energy waves 3014. Transducer 3012 is located at a firstlocation of an energy propagating medium. The emitted energy waves 3014propagate through the energy propagating medium. Receiver transducer3016 is located at a second location of the energy propagating medium.Receiver transducer 3016 captures the energy waves 3014, which are fedto analog mux 3020 and passed to the zero-crossing receiver 2900. Thecaptured energy waves by transducer 3016 are indicated by electricalwaves 3018 provided to mux 3020. Zero-crossing receiver 2900 outputs apulse corresponding to each zero crossing detected from capturedelectrical waves 3018. Alternatively, edge-detect receiver 2800 can beused to detect propagated energy waves. The zero crossings are countedand used to determine changes in the phase and frequency of the energywaves propagating through the energy propagating medium. In anon-limiting example, a parameter such as applied force is measured byrelating the measured phase and frequency to a known relationshipbetween the parameter (e.g. force) and the material properties of theenergy propagating medium. In general, pulse sequence 3022 correspondsto the detected signal frequency. The zero-crossing receiver 2900 is ina feedback path of the propagation tuned oscillator. The pulse sequence3022 is coupled through mux 3002 in a positive closed-loop feedbackpath. The pulse sequence 3022 disables the clock signal 3004 such thatthe path providing pulse sequence 3022 is coupled to driver 2700 tocontinue emission of energy waves into the energy propagating medium andthe path of clock signal 3004 to driver 2700 is disabled. The pulsesequence can comprise one or more pulses. Thus, closing the loopcontinues a process of energy wave emission, energy wave propagation,and detection of the energy wave in the energy propagation medium withthe detection generating a new signal to initiate a next emission.

FIG. 31 is an exemplary block diagram of a propagation tuned oscillator(PTO) incorporating the zero-crossing receiver 3140 for operation incontinuous wave mode. In particular, it illustrates closed loopmeasurement of the transit time of ultrasound waves within a waveguideby the operation of the propagation tuned oscillator as disclosedhereinabove. Alternatively, an edge-detect receiver can be used forenergy wave detection. This example is for operation in continuous wavemode. The system can also be operated in pulse mode and a pulse-echomode. Pulse mode and pulsed echo-mode use a pulsed energy wave.Pulse-echo mode uses reflection to direct an energy wave within theenergy propagation medium. Briefly, the digital logic circuit 3146digitizes the frequency of operation of the propagation tunedoscillator.

In continuous wave mode of operation a sensor comprising transducer3104, propagating structure 3102, and transducer 3106 is used to measurethe parameter. In general, the parameter to be measured affects theproperties of the propagating medium. For example, an external force orcondition 3112 is applied to propagating structure 3102 that changes thelength of the waveguide in a path of a propagating energy wave. A changein length corresponds to a change in transit time 3108 of thepropagating wave. Similarly, the length of propagating structure 3102corresponds to the applied force 3112. A length reduction corresponds toa higher force being applied to the propagating structure 3102.Conversely, a length increase corresponds to a lowering of the appliedforce 3112 to the propagating structure 3102. The length of propagatingstructure 3102 is measured and is converted to force by way of a knownlength to force relationship.

Transducer 3104 is an emitting device in continuous wave mode. Thesensor for measuring a parameter comprises transducer 3104 coupled topropagating structure 3102 at a first location. A transducer 3106 iscoupled to propagating structure 3102 at a second location. Transducer3106 is a receiving transducer for capturing propagating energy waves.In one embodiment, the captured propagated energy waves are electricalsine waves 3134 that are output by transducer 3106.

A measurement sequence is initiated when control circuitry 3118 closesswitch 3120 coupling oscillator output 3124 of oscillator 3122 to theinput of amplifier 3126. One or more pulses provided to amplifier 3126initiates an action to propagate energy waves 3110 having simple orcomplex waveforms through energy propagating structure or medium 3102.Amplifier 3126 comprises a digital driver 3128 and matching network3130. In one embodiment, amplifier 3126 transforms the oscillator outputof oscillator 3122 into sine waves of electrical waves 3132 having thesame repetition rate as oscillator output 3124 and sufficient amplitudeto excite transducer 3104.

Emitting transducer 3104 converts the sine waves 3132 into energy waves3110 of the same frequency and emits them at the first location intoenergy propagating structure or medium 3102. The energy waves 3110propagate through energy propagating structure or medium 3102. Uponreaching transducer 3106 at the second location, energy waves 3110 arecaptured, sensed, or detected. The captured energy waves are convertedby transducer 3106 into sine waves 3134 that are electrical waves havingthe same frequency.

Amplifier 3136 comprises a pre-amplifier 3138 and zero-cross receiver3140. Amplifier 3136 converts the sine waves 3134 into digital pulses3142 of sufficient duration to sustain the behavior of the closed loopcircuit. Control circuitry 3118 responds to digital pulses 3142 fromamplifier 3136 by opening switch 3120 and closing switch 3144. Openingswitch 3120 decouples oscillator output 3124 from the input of amplifier3126. Closing switch 3144 creates a closed loop circuit coupling theoutput of amplifier 3136 to the input of amplifier 3126 and sustainingthe emission, propagation, and detection of energy waves through energypropagating structure or medium 3102.

An equilibrium state is attained by maintaining unity gain around thisclosed loop circuit wherein sine waves 3132 input into transducer 3104and sine waves 3134 output by transducer 3106 are in phase with a smallbut constant offset. Transducer 3106 as disclosed above, outputs thesine waves 3134 upon detecting energy waves propagating to the secondlocation. In the equilibrium state, an integer number of energy waves3110 propagate through energy propagating structure or medium 3102.

Movement or changes in the physical properties of energy propagatingstructure or medium 3102 change a transit time 3108 of energy waves3110. The transit time 3108 comprises the time for an energy wave topropagate from the first location to the second location of propagatingstructure 3102. Thus, the change in the physical property of propagatingstructure 3102 results in a corresponding time period change of theenergy waves 3110 within energy propagating structure or medium 3102.These changes in the time period of the energy waves 3110 alter theequilibrium point of the closed loop circuit and frequency of operationof the closed loop circuit. The closed loop circuit adjusts such thatsine waves 3132 and 3134 correspond to the new equilibrium point. Thefrequency of energy waves 3110 and changes to the frequency correlate tochanges in the physical attributes of energy propagating structure ormedium 3102.

The physical changes may be imposed on energy propagating structure 3102by external forces or conditions 3112 thus translating the levels andchanges of the parameter or parameters of interest into signals that maybe digitized for subsequent processing, storage, and display.Translation of the operating frequency into digital binary numbersfacilitates communication, additional processing, storage, and displayof information about the level and changes in physical parameters ofinterest. Similarly, the frequency of energy waves 3110 during theoperation of the closed loop circuit, and changes in this frequency, maybe used to measure movement or changes in physical attributes of energypropagating structure or medium 3102.

Prior to measurement of the frequency or operation of the propagationtuned oscillator, control logic 3118 loads the loop count into digitalcounter 3150 that is stored in count register 3148. The first digitalpulses 3142 initiates closed loop operation within the propagation tunedoscillator and signals control circuit 3118 to start measurementoperations. At the start of closed loop operation, control logic 3118enables digital counter 3150 and digital timer 3152. In one embodiment,digital counter 3150 decrements its value on the rising edge of eachdigital pulse output by zero-crossing receiver 3140. Digital timer 3152increments its value on each rising edge of clock pulses 3156. When thenumber of digital pulses 3142 has decremented, the value within digitalcounter 3150 to zero a stop signal is output from digital counter 3150.The stop signal disables digital timer 3152 and triggers control circuit3118 to output a load command to data register 3154. Data register 3154loads a binary number from digital timer 3152 that is equal to theperiod of the energy waves or pulses times the value in counter 3148divided by clock period 3156. With a constant clock period 3156, thevalue in data register 3154 is directly proportional to the aggregateperiod of the energy waves or pulses accumulated during the measurementoperation. Duration of the measurement operation and the resolution ofmeasurements may be adjusted by increasing or decreasing the valuepreset in the count register 3148.

FIG. 32 is a sensor interface diagram incorporating the integratedzero-crossing receiver 2900 in a pulse multiplexing arrangement formaintaining positive closed-loop feedback in accordance with oneembodiment. In one embodiment, the circuitry other than the sensor isintegrated on an application specific integrated circuit (ASIC). Thepositive closed-loop feedback path of the circuit is illustrated by thebold line path. Initially, mux 3202 is enabled to couple one or moredigital pulses 3204 to the transducer driver 2700. Transducer driver2700 generates a pulse sequence 3208 corresponding to digital pulses3204. Analog mux 3210 is enabled to couple pulse sequence 3208 to thetransmitter transducer 3212. Transducer 3212 is coupled to a medium at afirst location. Transducer 3212 responds to pulse sequence 3208 andgenerates corresponding energy pulses 3214 that are emitted into themedium at the first location. The energy pulses 3214 propagate throughthe medium.

A receiver transducer 3216 is located at a second location on themedium. Receiver transducer 3216 captures the energy pulses 3214 andgenerates a corresponding signal of electrical pulses 3218. Transducer3216 is coupled to a mux 3220. Mux 3220 is enabled to couple tozero-cross receiver 2900. Electrical pulses 3218 from transducer 3216are coupled to zero-cross receiver 2900. Zero-cross receiver 2900 countszero crossings of electrical pulses 3218 to determine changes in phaseand frequency of the energy pulses responsive to an applied force, aspreviously explained. Alternatively edge-detect receiver 2800 could beused to detect propagated energy waves. Zero-cross receiver 2900 outputsa pulse sequence 3222 corresponding to the detected signal frequency.Pulse sequence 3222 is coupled to mux 3202. Mux 3202 is decoupled fromcoupling digital pulses 3204 to driver 2700 upon detection of pulses3222. Simultaneously, mux 3202 is enabled to couple pulses 3222 todriver 2700 upon detection of pulses 3222 thereby creating a positiveclosed-loop feedback path. Thus, in pulse mode, zero-cross receiver 2900is part of the closed-loop feedback path that continues emission ofenergy pulses into the medium at the first location and detection at thesecond location to measure a transit time and changes in transit time ofpulses through the medium.

FIG. 33 is an exemplary block diagram of a propagation tuned oscillator(PTO) incorporating the zero-crossing receiver 3140 for operation inpulse mode. In particular, it illustrates closed loop measurement of thetransit time of ultrasound waves within a waveguide by the operation ofa propagation tuned oscillator as disclosed above. This example is foroperation in pulse mode. The system can also be operated in continuouswave mode, pulse mode, and pulse-echo mode. Continuous wave mode uses acontinuous wave signal. Pulse-echo mode uses reflection to direct anenergy wave within the energy propagation medium. Briefly, the digitallogic circuit 3146 digitizes the frequency of operation of thepropagation tuned oscillator.

In pulse mode of operation, a sensor comprising transducer 3104,propagating structure 3102, and transducer 3106 is used to measure theparameter. In general, the parameter to be measured affects theproperties of the propagating medium. For example, an external force orcondition 3112 is applied to propagating structure 3102 that changes thelength of the waveguide in a path of a propagating energy wave. A changein length corresponds to a change in transit time 3108 of thepropagating wave. The length of propagating structure 3102 is measuredand is converted to a force measurement by way of a known length toforce relationship. One benefit of pulse mode operation is the use of ahigh magnitude pulsed energy wave. In one embodiment, the magnitude ofthe energy wave decays as it propagates through the medium. The use of ahigh magnitude pulse is a power efficient method to produce a detectablesignal if the energy wave has to traverse a substantial distance or issubject to a reduction in magnitude as it propagated due to the medium.

A measurement sequence is initiated when control circuitry 3118 closesswitch 3120 coupling oscillator output 3124 of oscillator 3122 to theinput of amplifier 3126. One or more pulses provided to amplifier 3126initiates an action to propagate energy waves 3110 having simple orcomplex waveforms through energy propagating structure or medium 3102.Amplifier 3126 comprises a digital driver 3128 and matching network3130. In one embodiment, amplifier 3126 transforms the oscillator outputof oscillator 3122 into analog pulses of electrical waves 3332 havingthe same repetition rate as oscillator output 3124 and sufficientamplitude to excite transducer 3104.

Emitting transducer 3104 converts the analog pulses 3332 into energywaves 3110 of the same frequency and emits them at a first location intoenergy propagating structure or medium 3102. The energy waves 3110propagate through energy propagating structure or medium 3102. Uponreaching transducer 3106 at the second location, energy waves 3110 arecaptured, sensed, or detected. The captured energy waves are convertedby transducer 3106 into analog pulses 3334 that are electrical waveshaving the same frequency as energy waves 3110.

Amplifier 3136 comprises a pre-amplifier 3138 and zero-cross receiver3140. Amplifier 3136 converts the analog pulses 3334 into digital pulses3142 of sufficient duration to sustain the behavior of the closed loopcircuit. Alternatively, detection can be achieved using an edge detectreceiver. Control circuitry 3118 responds to digital pulses 3142 fromamplifier 3136 by opening switch 3120 and closing switch 3144. Openingswitch 3120 decouples oscillator output 3124 from the input of amplifier3126. Closing switch 3144 creates a closed loop circuit coupling theoutput of amplifier 3136 to the input of amplifier 3126 and sustainingthe emission, propagation, and detection of energy waves through energypropagating structure or medium 3102.

An equilibrium state is attained by maintaining unity gain around thisclosed loop circuit wherein pulses 3332 input into transducer 3104 andpulses 3334 output by transducer 3106 are in phase with a small butconstant offset. Transducer 3106 as disclosed above, outputs the pulses3334 upon detecting energy waves propagating to the second location. Inthe equilibrium state, an integer number of energy waves 3110 propagatethrough energy propagating structure or medium 3102.

Movement or changes in the physical properties of energy propagatingstructure or medium 3102 change a transit time 3108 of energy waves3110. The transit time 3108 comprises the time for an energy wave topropagate from the first location to the second location of propagatingstructure 3102. Thus, the change in the physical property of propagatingstructure 3102 results in a corresponding time period change of theenergy waves 3110 within energy propagating structure or medium 3102.These changes in the time period of the energy waves 3110 alter theequilibrium point of the closed loop circuit and frequency of operationof the closed loop circuit. The closed loop circuit adjusts such thatpulses 3332 and 3334 correspond to the new equilibrium point. Thefrequency of energy waves 3110 and changes to the frequency correlate tochanges in the physical attributes of energy propagating structure ormedium 3102.

The physical changes may be imposed on energy propagating structure 3102by external forces or conditions 3112 thus translating the levels andchanges of the parameter or parameters of interest into signals that maybe digitized for subsequent processing, storage, and display.Translation of the operating frequency into digital binary numbersfacilitates communication, additional processing, storage, and displayof information about the level and changes in physical parameters ofinterest as disclosed in more detail hereinabove. Similarly, thefrequency of energy waves 3110 during the operation of the closed loopcircuit, and changes in this frequency, may be used to measure movementor changes in physical attributes of energy propagating structure ormedium 3102.

FIG. 34 is a sensor interface diagram incorporating the edge-detectreceiver circuit 2800 in a pulse-echo multiplexing arrangement formaintaining positive closed-loop feedback in accordance with oneembodiment. The positive closed-loop feedback of the circuit isillustrated by the bold line path. Initially, multiplexer (mux) 3402receives as input a digital pulse 3404, which is passed to thetransducer driver 2700 to produce the pulse sequence 3408. Analogmultiplexer (mux) 3410 receives pulse sequence 3408, which is passed tothe transducer 3412 to generate energy pulses 3414. Energy pulses 3414are emitted into a first location of a medium. Energy pulses 3414propagate through the medium towards a second location having areflective surface 3416. In the pulse-echo example, energy pulses 3414are reflected off surface 3416 at the second location of the medium, forexample, the end of a waveguide or reflector, and echoed back to thetransducer 3412.

The transducer 3412 proceeds to capture the reflected pulse echo. Inpulsed echo mode, the transducer 3412 performs as both a transmitter anda receiver. As disclosed above, transducer 3412 toggles back and forthbetween emitting and receiving energy waves. Transducer 3412 capturesthe reflected echo pulses, which are coupled to analog mux 3410 anddirected to the edge-detect receiver 2800. The captured reflected echopulses are indicated by electrical waves 3418. Edge-detect receiver 2800locks on to a leading edge of signal 3418 corresponding to the wavefront of a propagated energy wave to determine changes in phase andfrequency of the energy pulses 3414 responsive to an applied force, aspreviously explained. In the embodiment, the energy wave is a reflectedpulsed energy wave. Alternatively, zero-crossing receiver 2900 can beused to detect the captured reflected echo pulses.

Among other parameters, edge-detect receiver 2800 generates a pulsesequence 3420 corresponding to the detected signal frequency. The pulsesequence 3420 is coupled to mux 3402 and directed to driver 2700 toinitiate one or more energy waves being emitted into the medium bytransducer 3412. Pulse 3404 is decoupled from being provided to driver2700. Thus, a positive closed loop feedback is formed that repeatablyemits energy waves into the medium until mux 3402 prevents a signal frombeing provided to driver 2700.

FIG. 35 is an exemplary block diagram of a propagation tuned oscillator(PTO) incorporating the edge-detect receiver circuit 3440 for operationin pulse echo mode. In particular, it illustrates closed loopmeasurement of a transit time of reflected ultrasound waves propagatingwithin the waveguide by the operation of a propagation tuned oscillatoras disclosed above. This example is for operation in a pulse echo mode.The system can also be operated in pulse mode and a continuous wavemode. Pulse mode does not use a reflected signal. Continuous wave modeuses a continuous signal. Briefly, the digital logic circuit 3446digitizes the frequency of operation of the propagation tunedoscillator.

In pulse-echo mode of operation a sensor comprising transducer 3404,propagating structure 3402, and reflecting surface 3406 is used tomeasure the parameter. In general, the parameter to be measured affectsthe properties of the propagating medium. For example, an external forceor condition 3412 is applied to propagating structure 3402 that changesthe length of the waveguide in a path of a propagating energy wave. Achange in length corresponds to a change in transit time of thepropagating wave. Similarly, the length of propagating structure 3402corresponds to the applied force 3412. A length reduction corresponds toa higher force being applied to the propagating structure 3402.Conversely, a length increase corresponds to a lowering of the appliedforce 3412 to the propagating structure 3402. The length of propagatingstructure 3402 is measured and is converted to force by way of a knownlength to force relationship.

Transducer 3404 is both an emitting device and a receiving device inpulse-echo mode. The sensor for measuring a parameter comprisestransducer 3404 coupled to propagating structure 3402 at a firstlocation. A reflecting surface is coupled to propagating structure 3402at a second location. Transducer 3404 has two modes of operationcomprising an emitting mode and receiving mode. Transducer 3404 emits anenergy wave into the propagating structure 3402 at the first location inthe emitting mode. The energy wave propagates to a second location andis reflected by reflecting surface 3406. The reflected energy wave isreflected towards the first location. Transducer 3404 subsequentlyreceives the reflected energy wave and generates a signal in thereceiving mode corresponding to the reflected energy wave.

A measurement sequence in pulse echo mode is initiated when controlcircuitry 3418 closes switch 3420 coupling digital output 3424 ofoscillator 3422 to the input of amplifier 3426. One or more pulsesprovided to amplifier 3426 starts a process to emit one or more energywaves 3410 having simple or complex waveforms into energy propagatingstructure or medium 3402. Amplifier 3426 comprises a digital driver 3428and matching network 3430. In one embodiment, amplifier 3426 transformsthe digital output of oscillator 3422 into pulses of electrical waves3432 having the same repetition rate as digital output 3424 andsufficient amplitude to excite transducer 3404.

Transducer 3404 converts the pulses of electrical waves 3432 into pulsesof energy waves 3410 of the same repetition rate and emits them intoenergy propagating structure or medium 3402. The pulses of energy waves3410 propagate through energy propagating structure or medium 3402 asshown by energy wave propagation 3414 towards reflecting surface 3406.Upon reaching reflecting surface 3406, energy waves 3410 are reflectedby reflecting surface 3406. Reflected energy waves propagate towardstransducer 3404 as shown by energy wave propagation 3416. The reflectedenergy waves are detected by transducer 3404 and converted into pulsesof electrical waves 3434 having the same repetition rate.

Amplifier 3436 comprises a pre-amplifier 3438 and edge-detect receiver3440. Amplifier 3436 converts the pulses of electrical waves 3434 intodigital pulses 3442 of sufficient duration to sustain the pulse behaviorof the closed loop circuit. Control circuitry 3418 responds to digitaloutput pulses 3442 from amplifier 3436 by opening switch 3420 andclosing switch 3444. Opening switch 3420 decouples oscillator output3424 from the input of amplifier 3426. Closing switch 3444 creates aclosed loop circuit coupling the output of amplifier 3436 to the inputof amplifier 3426 and sustaining the emission, propagation, anddetection of energy pulses through energy propagating structure ormedium 3402.

An equilibrium state is attained by maintaining unity gain around thisclosed loop circuit wherein electrical waves 3432 input into transducer3404 and electrical waves 3434 output by transducer 3404 are in phasewith a small but constant offset. Transducer 3404 as disclosed above,outputs the electrical waves 3434 upon detecting reflected energy wavesreflected from reflecting surface 3406. In the equilibrium state, aninteger number of pulses of energy waves 3410 propagate through energypropagating structure or medium 3402.

Movement or changes in the physical properties of energy propagatingstructure or medium 3402 change a transit time 3408 of energy waves3410. The transit time 3408 comprises the time for an energy wave topropagate from the first location to the second location of propagatingstructure 3402 and the time for the reflected energy wave to propagatefrom the second location to the first location of propagating structure3402. Thus, the change in the physical property of propagating structure3402 results in a corresponding time period change of the energy waves3410 within energy propagating structure or medium 3402. These changesin the time period of the repetition rate of the energy pulses 3410alter the equilibrium point of the closed loop circuit and repetitionrate of operation of the closed loop circuit. The closed loop circuitadjusts such that electrical waves 3432 and 3434 correspond to the newequilibrium point. The repetition rate of energy waves 3410 and changesto the repetition rate correlate to changes in the physical attributesof energy propagating structure or medium 3402.

The physical changes may be imposed on energy propagating structure 3402by external forces or conditions 3412 thus translating the levels andchanges of the parameter or parameters of interest into signals that maybe digitized for subsequent processing, storage, and display.Translation of the operating frequency into digital binary numbersfacilitates communication, additional processing, storage, and displayof information about the level and changes in physical parameters ofinterest. Similarly, the frequency of energy waves 3410 during theoperation of the closed loop circuit, and changes in this frequency, maybe used to measure movement or changes in physical attributes of energypropagating structure or medium 3402.

Prior to measurement of the frequency or operation of the propagationtuned oscillator, control circuitry 3418 loads the loop count intodigital counter 3450 that is stored in count register 3448. The firstdigital pulses 3442 initiates closed loop operation within thepropagation tuned oscillator and signals control circuit 3418 to startmeasurement operations. At the start of closed loop operation, controlcircuit 3418 enables digital counter 3450 and digital timer 3452. In oneembodiment, digital counter 3450 decrements its value on the rising edgeof each digital pulse output by edge-detect receiver 3440. Digital timer3452 increments its value on each rising edge of clock pulses 3456. Astop signal is output from digital counter 3450 when digital pulses 3442has decremented the value within digital counter 3450 to zero. The stopsignal disables digital timer 3452 and triggers control circuit 3418 tooutput a load command to data register 3454. Data register 3454 loads abinary number from digital timer 3452 that is equal to the period of theenergy waves or pulses times the value in counter 3448 divided by clockperiod 3456. With a constant clock period 3456, the value in dataregister 3454 is directly proportional to the aggregate period of theenergy waves or pulses accumulated during the measurement operation.Duration of the measurement operation and the resolution of measurementsmay be adjusted by increasing or decreasing the value preset in thecount register 3448.

FIG. 36 is a final insert 3602 in accordance with an exemplaryembodiment. In the example, the final insert 3602 is a prostheticcomponent for a total knee reconstruction. Insert 3602 comprises twobearing surfaces that couple to the condyles of a femur or femoralprosthetic component. A bottom surface of insert 3602 couples to a majorsurface of the tibial implant. The final insert 3602 is an active devicefor measuring a parameter of the muscular-skeletal system. A sensingmodule 3604 as disclosed hereinabove underlies each bearing surface ofinsert 3602. In one embodiment, a contacting surface of insert 3602couples to the bearing surface. In one embodiment, insert 3602 has aconformal surface that is similar to the bearing surface. The finalinsert 3602 is a permanent or quasi-permanent member of the jointprosthesis that provides long term post-operative sensing of the joint.Quasi-permanent refers to the fact that insert 3602 has a wear surfacethat has a finite life time that could need replacing depending on anumber of factors such as life style, physical shape, and length of use.Final insert 3602 replaces a passive insert that has no sensingcapability. In one embodiment, an external charging device proximallylocated to the knee prosthetics can inductively charge the sensingmodule 3604. A super capacitor is charged in sensing module 3604 thatpowers the sensor and circuitry to perform the one or more measurements.Alternatively, a battery or other temporary energy storage device can beused to power sensing module 3604 and be charged with the externalcharging device.

FIG. 37 is a perspective view of sensing modules 3604 in final insert3602 in accordance with an exemplary embodiment. Final insert 3602 isshown being separated in two halves via a horizontal cut to show sensingmodules 3604. Final insert 3602 is used in a total knee reconstructionwhere both knee compartments are replaced. A single sensing module 3604would be used for a partial reconstruction. Bearing surfaces 3704 coupleto a femoral prosthetic component (not shown) such that the articulatingsurfaces allow movement of the muscular-skeletal system. In the example,a bottom surface 3706 of the final insert 3602 aligns and couples to atibial prosthetic component. In the example, the bottom surface 3706 isa support surface that retains insert 3602 in a fixed position relativeto a mechanical axis of the leg. Furthermore, the bottom surface 3706and a surface of the tibial prosthetic component are non-articulating.

Sensing modules 3604 underlie bearing surfaces 3704. A parameter of themuscular-skeletal system is applied to the bearing surface 3704 andcouples through the material of final insert 3602 to contacting surfaces3702 of sensing modules 3604. The bearing surfaces 3704 are typically ahigh strength polymer such as ultra high molecular weight polyethylene.In a non-limiting example, a force, pressure, or load is the parametermeasured by sensing module 3604. Sensing module 3604 can measureparameter magnitude and the location where the parameter is applied.Sensing module 3604 can have a surface that mirrors or replicates thesurface of bearing surfaces 3704.

In one embodiment, the final insert 3602 can be precision molded in twoor more pieces that allow the positioning and insertion of sensingmodule 3604. As shown, the final insert is formed in two halves. Theupper half includes the bearing surfaces 3704. The insert can be formedof a composite material. The composite material will at least includethe bearing surface material and a second material that is attached orbonded together. A cavity is formed in predetermined locations thatreceive sensing modules 3604. The cavities correspond to bearingsurfaces 3604 for each compartment of the knee. The sensing modules 3604are placed in each cavity. The halves of final insert 3602 are thenfastened together whereby the contacting surface 3702 operativelycouples to a corresponding bearing surface 3704. The contact surfaces3702 have a relational position to bearing surfaces 3604 allowingposition detection where the parameter is applied. The halves of finalinsert 3602 can be mechanically fastened, attached by adhesive,thermally bonded, or connected by other method such that halves will notseparate under all operating conditions. The fastening process can alsoform a seal that isolates sensing modules 3604 from the externalenvironment.

FIG. 38 is an illustration of the final insert 3602 installed in a kneein accordance with an exemplary embodiment. In the example, a femoralprosthetic component 3710 is coupled to a prepared 3714 femur.Similarly, a tibial prosthetic component 3712 is coupled to a preparedtibia 3716. The preparation includes alignment of the prostheticcomponents to a mechanical axis. The insert 3602 is placed between thetibial prosthetic component 3712 and femoral prosthetic component 3710.In general, the insert 3602 is substantially equivalent in dimensions toa passive final insert. The artificial condyles of femoral prostheticcomponent 3710 articulate with a bearing surface of final insert 3602that allows movement of the leg.

As disclosed above, final insert 3602 includes a sensing module that cantransmit data to a processor 3708. The processor can be in a tool,equipment, computer, display, or other device. As shown, the processoris in a notebook computer. Receiver circuitry is coupled to processor3708 that can communicate with the sensing module. Typically, thereceiver circuitry is placed in close proximity to final insert 3602 toreceive the short-range transmission. In one embodiment, the sensingmodule can only transmit data. In a second embodiment, the sensingmodule can have two-way communication between the sensing module andprocessor 3708.

The loading, balance, and position can be adjusted during surgery withinpredetermined quantitatively measured ranges through surgical techniquesand adjustments using data from a trial insert and final insert 3602.Both the trial and final inserts include the sensing module to providemeasured data to processor 3708 for display. The final insert 3602 isalso used to monitor the reconstructed joint long term. The data can beused by the patient and health care providers to ensure that the jointis functioning properly during rehabilitation and as the patient returnsto an active normal lifestyle. Conversely, the patient or health careprovider is notified when the measured parameters are out ofspecification. This provides early detection of a problem that can beresolved with minimal stress to the patient. The data from final insert3602 can be displayed on a screen in real time using data from theembedded sensing module. In one embodiment, a handheld device is used toreceive data from final insert 3602. The handheld device can be held inproximity to the knee allowing a strong signal to be obtained forreception of the data.

In general, final insert 3602 is an example of a sensor system that canbe integrated into prosthetic components. The form factor of the sensingassemblages, layout architecture, electronic circuitry, and housingallow it to fit in one or more prosthetic components. Moreover, it is aself-contained device that performs measurements without extraneousdevices. The sensing module can also be placed in femoral prostheticcomponent 3710 or tibial prosthetic component 3712 to measure aparameter of interest. Data generated by the device can be sent to adatabase for analysis.

Artificial components for other joint replacement surgeries have asimilar operational form as the knee joint example. The joint typicallycomprises two or more bones with a cartilaginous surface as a bearingsurface that allows joint movement. The cartilage also acts to absorbloading on the joint and prevents bone-to-bone contact. Reconstructionof the hip, spine, shoulder, and other joints has similar functioninginsert structures having at least one bearing surface. Like the kneejoint, these other insert structures typically comprise a polymermaterial. The polymer material is formed for a particular jointstructure. For example, the hip insert is formed in a cup shape that isfitted into the pelvis. In general, the size and thickness of theseother joint inserts allow the integration of the sensing module. Itshould be noted that the sensing module disclosed herein contemplatesuse in both trial inserts and permanent inserts for the other joints ofthe muscular-skeletal system thereby providing quantitative parametermeasurements during and post surgery.

While the present invention has been described with reference toparticular embodiments, those skilled in the art will recognize thatmany changes may be made thereto without departing from the spirit andscope of the present invention. Each of these embodiments and obviousvariations thereof is contemplated as falling within the spirit andscope of the invention.

1. A sensing module for measuring a force, pressure, or load applied bythe muscular-skeletal system comprising: a first surface for coupling tothe muscular-skeletal system where the first surface includes apredetermined area comprising a polygon; a second surface; and at leastthree force, pressure, or load sensors coupled between the first andsecond surfaces where each sensor underlies a vertex of the polygon,where the sensing module is configured to measure the force, pressure,or load applied by the muscular-skeletal system, and where the sensingmodule is configured to identify a position of applied load on the firstsurface.
 2. The sensing module of claim 1 further including: electroniccircuitry coupled to the at least three force, pressure, or loadsensors; a transmitter coupled to the electronic circuitry configured totransmit sensor data; and a power source configured to power theelectronic circuitry and transmitter.
 3. The sensing module of claim 2further includes an encapsulating enclosure to house the electroniccircuitry, transmitter, power source, and the at least three force,pressure, or load sensors.
 4. The sensing module of claim 3 where thepolygon is a triangle.
 5. The sensing module of claim 4 furtherincluding a flexible interconnect coupling the electronic circuitry tothe at least three force, pressure, or load sensors.
 6. The sensingmodule of claim 5 further including a remote system configured toreceive and display data from the sensing module.
 7. The sensing moduleof claim 6 further including a structure configured to distributeloading applied to the first surface to the at least three force,pressure, or load sensors.
 8. The sensing module of claim 7 where thefirst surface is configured to move under a force, pressure, or load. 9.The sensing module of claim 8 where the at least three force, pressure,or load sensors are piezo-resistive sensors.
 10. The sensing module ofclaim 1 where the electronic circuitry underlies the at least threeforce, pressure, or load sensors.
 11. A sensing module for measuring aforce, pressure, or load applied by the muscular-skeletal systemcomprising: a first surface for coupling to the muscular-skeletal systemwhere the first surface includes a predetermined area comprising apolygon; a second surface; at least three force, pressure, or loadsensors coupled between the first and second surfaces where each sensorunderlies a vertex of the polygon, where the sensing module isconfigured to measure a force, pressure, or load applied by themuscular-skeletal system to the first surface, and where the sensingmodule is configured to identify a position of applied load on the firstsurface; and at least one structure to distribute loading coupledbetween the first surface and the at least three force, pressure, orload sensors.
 12. The sensing module of claim 11 where the sensingmodule is configured to measure a force, pressure, or load applied bythe muscular-skeletal system within the predetermined area and where thesensing module is configured to identify the position of applied loadwithin the predetermined area.
 13. The sensing module of claim 12 wherethe polygon is a triangle.
 14. The sensing module of claim 13 where thesensing module is an insert prosthetic component further comprising:electronic circuitry coupled to the at least three force, pressure, orload sensors; a transmitter coupled to the electronic circuitryconfigured to transmit sensor data; and a power source configured topower the electronic circuitry and transmitter.
 15. The sensing moduleof claim 14 where the electronic circuitry, transmitter, power source,and at least three force, pressure, or load sensors are housed in theinsert prosthetic component and isolated from an external environment.16. The sensing module of claim 15 where the first surface is anarticular surface.
 17. The sensing module of claim 16 where the sensingmodule is configured to send data such that the force, pressure, andload and position of applied load is displayed on a remote system inreal time and where the at least three force, pressure, or load sensorscomprises one of a piezo-resistive sensor, MEMS sensor, strain gauge, ormechanical sensor.
 18. A sensing module for measuring a force, pressure,or load applied by the muscular-skeletal system comprising: a firstsurface for coupling to the muscular-skeletal system where the firstsurface includes a predetermined area comprising a polygon; a secondsurface; and at least three piezo-resistive sensors coupled between thefirst and second surfaces where each sensor underlies a vertex of thepolygon, where the sensing module is configured to measure the force,pressure, or load applied by the muscular-skeletal system, and where thesensing module is configured to identify a position of applied load onthe first surface.
 19. The sensing module of claim 18 where the sensingmodule is configured to measure a force, pressure, or load applied bythe muscular-skeletal system within the predetermined area and where thesensing module is configured to identify the position of applied loadwithin the predetermined area.
 20. The sensing module of claim 19 whereat least one structure to distribute loading is coupled between thefirst surface and the at least three piezo-resistive sensors.